Charged particle cancer therapy beam path control method and apparatus

ABSTRACT

The invention comprises a charged particle beam path coupling an injector, synchrotron accelerator, beam transport system, targeting system, and/or patient interface method and apparatus. Preferably, the injector comprises: a negative ion beam source, a two phase ion source vacuum system, an ion beam focusing lens, and/or a tandem accelerator. Preferably, the synchrotron comprises turning magnets, edge focusing magnets, magnetic field concentration magnets, winding and correction coils, flat magnetic field incident surfaces, and/or extraction elements. Preferably, the synchrotron, beam transport system, targeting system, and patient interface combine to allow multi-axis/multi-field irradiation, where multi-axis control comprises control of horizontal and vertical beam position, beam energy, and/or beam intensity and multi-field control comprises control of patient rotation and distribution of delivered energy in and about the tumor in a time controlled, targeted, accurate, precise, dosage controlled, and/or efficient manner.

CROSS-REFERENCES TO RELATED APPLICATIONS

This application:

-   -   is a continuation-in-part of U.S. patent application Ser. No.         12/425,683 filed Apr. 17, 2009, which claims the benefit of:         -   U.S. provisional patent application No. 61/055,395 filed May             22, 2008;         -   U.S. provisional patent application No. 61/137,574 filed             Aug. 1, 2008;         -   U.S. provisional patent application No. 61/192,245 filed             Sep. 17, 2008;         -   U.S. provisional patent application No. 61/055,409 filed May             22, 2008;         -   U.S. provisional patent application No. 61/203,308 filed             Dec. 22, 2008;         -   U.S. provisional patent application No. 61/188,407 filed             Aug. 11, 2008;         -   U.S. provisional patent application No. 61/188,406 filed             Aug. 11, 2008;         -   U.S. provisional patent application No. 61/189,815 filed             Aug. 25, 2008;         -   U.S. provisional patent application No. 61/201,731 filed             Dec. 15, 2008;         -   U.S. provisional patent application No. 61/205,362 filed             Jan. 12, 2009;         -   U.S. provisional patent application No. 61/134,717 filed             Jul. 14, 2008;         -   U.S. provisional patent application No. 61/134,707 filed             Jul. 14, 2008;         -   U.S. provisional patent application No. 61/201,732 filed             Dec. 15, 2008;         -   U.S. provisional patent application No. 61/198,509 filed             Nov. 7, 2008;         -   U.S. provisional patent application No. 61/134,718 filed             Jul. 14, 2008;         -   U.S. provisional patent application No. 61/190,613 filed             Sep. 2, 2008;         -   U.S. provisional patent application No. 61/191,043 filed             Sep. 8, 2008;         -   U.S. provisional patent application No. 61/192,237 filed             Sep. 17, 2008;         -   U.S. provisional patent application No. 61/201,728 filed             Dec. 15, 2008;         -   U.S. provisional patent application No. 61/190,546 filed             Sep. 2, 2008;         -   U.S. provisional patent application No. 61/189,017 filed             Aug. 15, 2008;         -   U.S. provisional patent application No. 61/198,248 filed             Nov. 5, 2008;         -   U.S. provisional patent application No. 61/198,508 filed             Nov. 7, 2008;         -   U.S. provisional patent application No. 61/197,971 filed             Nov. 3, 2008;         -   U.S. provisional patent application No. 61/199,405 filed             Nov. 17, 2008;         -   U.S. provisional patent application No. 61/199,403 filed             Nov. 17, 2008; and         -   U.S. provisional patent application No. 61/199,404 filed             Nov. 17, 2008;     -   is a continuation-in-part of U.S. patent application Ser. No.         12/687,387 filed Jan. 14, 2010, which         -   is a continuation-in-part of U.S. patent application Ser.             No. 12/425,683 filed Apr. 17, 2009;         -   claims the benefit of U.S. provisional patent application             No. 61/209,529 filed Mar. 9, 2009;         -   claims the benefit of U.S. provisional patent application             No. 61/208,182 filed Feb. 23, 2009;         -   claims the benefit of U.S. provisional patent application             No. 61/208,971 filed Mar. 3, 2009; and         -   claims the benefit of U.S. provisional patent application             No. 61/270,298, filed Jul. 7, 2009; and     -   claims the benefit of U.S. provisional patent application No.         61/308,621, filed Feb. 26, 2010; and     -   claims priority to PCT patent application serial No.:         PCT/RU2009/00015, filed Mar. 4, 2009,     -   all of which are incorporated herein in their entirety by this         reference thereto.

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention relates generally to treatment of solid cancers. More particularly, the invention relates to a charged particle cancer therapy method and apparatus.

2. Discussion of the Prior Art

Cancer

A tumor is an abnormal mass of tissue. Tumors are either benign or malignant. A benign tumor grows locally, but does not spread to other parts of the body. Benign tumors cause problems because of their spread, as they press and displace normal tissues. Benign tumors are dangerous in confined places such as the skull. A malignant tumor is capable of invading other regions of the body. Metastasis is cancer spreading by invading normal tissue and spreading to distant tissues.

Cancer Treatment

Several distinct forms of radiation therapy exist for cancer treatment including: brachytherapy, traditional electromagnetic X-ray therapy, and proton therapy. Proton therapy systems typically include: a beam generator, an accelerator, and a beam transport system to move the resulting accelerated protons to a plurality of treatment rooms where the protons are delivered to a tumor in a patient's body.

Proton therapy works by aiming energetic ionizing particles, such as protons accelerated with a particle accelerator, onto a target tumor. These particles damage the DNA of cells, ultimately causing their death. Cancerous cells, because of their high rate of division and their reduced ability to repair damaged DNA, are particularly vulnerable to attack on their DNA.

Charged Particle Cancer Therapy

Patents related to the current invention are summarized here.

Proton Beam Therapy System

F. Cole, et. al. of Loma Linda University Medical Center “Multi-Station Proton Beam Therapy System”, U.S. Pat. No. 4,870,287 (Sep. 26, 1989) describe a proton beam therapy system for selectively generating and transporting proton beams from a single proton source and accelerator to a selected treatment room of a plurality of patient treatment rooms.

Accelerator/Synchrotron

S. Peggs, et. al. “Rapid Cycling Medical Synchrotron and Beam Delivery System”, U.S. Pat. No. 7,432,516 (Oct. 7, 2008) describe a synchrotron having combined function magnets and a radio frequency (RF) cavity accelerator. The combined function magnets function to first bend the particle beam along an orbital path and second focus the particle beam. The RF cavity accelerator is a ferrite loaded cavity adapted for high speed frequency swings for rapid cycling particle acceleration.

H. Tanaka, et. al. “Charged Particle Accelerator”, U.S. Pat. No. 7,259,529 (Aug. 21, 2007) describe a charged particle accelerator having a two period acceleration process with a fixed magnetic field applied in the first period and a timed second acceleration period to provide compact and high power acceleration of the charged particles.

T. Haberer, et. al. “Ion Beam Therapy System and a Method for Operating the System”, U.S. Pat. No. 6,683,318 (Jan. 27, 2004) describe an ion beam therapy system and method for operating the system. The ion beam system uses a gantry that has a vertical deflection system and a horizontal deflection system positioned before a last bending magnet that result in a parallel scanning mode resulting from an edge focusing effect.

V. Kulish, et. al. “Inductional Undulative EH-Accelerator”, U.S. Pat. No. 6,433,494 (Aug. 13, 2002) describe an inductive undulative EH-accelerator for acceleration of beams of charged particles. The device consists of an electromagnet undulation system, whose driving system for electromagnets is made in the form of a radio-frequency (RF) oscillator operating in the frequency range from about 100 KHz to 10 GHz.

K. Saito, et. al. “Radio-Frequency Accelerating System and Ring Type Accelerator Provided with the Same”, U.S. Pat. No. 5,917,293 (Jun. 29, 1999) describe a radio-frequency accelerating system having a loop antenna coupled to a magnetic core group and impedance adjusting means connected to the loop antenna. A relatively low voltage is applied to the impedance adjusting means allowing small construction of the adjusting means.

J. Hirota, et. al. “Ion Beam Accelerating Device Having Separately Excited Magnetic Cores”, U.S. Pat. No. 5,661,366 (Aug. 26, 1997) describe an ion beam accelerating device having a plurality of high frequency magnetic field inducing units and magnetic cores.

J. Hirota, et. al. “Acceleration Device for Charged Particles”, U.S. Pat. No. 5,168,241 (Dec. 1, 1992) describe an acceleration cavity having a high frequency power source and a looped conductor operating under a control that combine to control a coupling constant and/or de-tuning allowing transmission of power more efficiently to the particles.

Extraction

T. Nakanishi, et. al. “Method of Operating the Particle Beam Radiation Therapy System”, U.S. Pat. No. 7,122,978 (Oct. 17, 2006) describe a charged particle beam accelerator having an RF-KO unit for increasing amplitude of betatron oscillation of a charged particle beam within a stable region of resonance and an extraction quadrupole electromagnet unit for varying a stable region of resonance. The RF-KO unit is operated within a frequency range in which the circulating beam does not go beyond a boundary of stable region of resonance and the extraction quadrupole electromagnet is operated with timing required for beam extraction.

T. Haberer, et. al. “Method and Device for Controlling a Beam Extraction Raster Scan Irradiation Device for Heavy Ions or Protons”, U.S. Pat. No. 7,091,478 (Aug. 15, 2006) describe a method for controlling beam extraction in terms of beam energy, beam focusing, and beam intensity for every accelerator cycle.

K. Hiramoto, et. al. “Accelerator and Medical System and Operating Method of the Same”, U.S. Pat. No. 6,472,834 (Oct. 29, 2002) describe a cyclic type accelerator having a deflection electromagnet and four-pole electromagnets for making a charged particle beam circulate, a multi-pole electromagnet for generating a stability limit of resonance of betatron oscillation, and a high frequency source for applying a high frequency electromagnetic field to the beam to move the beam to the outside of the stability limit. The high frequency source generates a sum signal of a plurality of alternating current (AC) signals of which the instantaneous frequencies change with respect to time, and of which the average values of the instantaneous frequencies with respect to time are different. The system applies the sum signal via electrodes to the beam.

K. Hiramoto, et. al. “Synchrotron Type Accelerator and Medical Treatment System Employing the Same”, U.S. Pat. No. 6,087,670 (Jul. 11, 2000) and K. Hiramoto, et. al. “Synchrotron Type Accelerator and Medical Treatment System Employing the Same”, U.S. Pat. No. 6,008,499 (Dec. 28, 1999) describe a synchrotron accelerator having a high frequency applying unit arranged on a circulating orbit for applying a high frequency electromagnetic field to a charged particle beam circulating and for increasing amplitude of betatron oscillation of the particle beam to a level above a stability limit of resonance. Additionally, for beam ejection, four-pole divergence electromagnets are arranged: (1) downstream with respect to a first deflector; (2) upstream with respect to a deflecting electromagnet; (3) downstream with respect to the deflecting electromagnet; and (4) and upstream with respect to a second deflector.

K. Hiramoto, et. al. “Circular Accelerator and Method and Apparatus for Extracting Charged-Particle Beam in Circular Accelerator”, U.S. Pat. No. 5,363,008 (Nov. 8, 1994) describe a circular accelerator for extracting a charged-particle beam that is arranged to: (1) increase displacement of a beam by the effect of betatron oscillation resonance; (2) to increase the betatron oscillation amplitude of the particles, which have an initial betatron oscillation within a stability limit for resonance; and (3) to exceed the resonance stability limit thereby extracting the particles exceeding the stability limit of the resonance.

K. Hiramoto, et. al. “Method of Extracting Charged Particles from Accelerator, and Accelerator Capable Carrying Out the Method, by Shifting Particle Orbit”, U.S. Pat. No. 5,285,166 (Feb. 8, 1994) describe a method of extracting a charged particle beam. An equilibrium orbit of charged particles maintained by a bending magnet and magnets having multipole components greater than sextuple components is shifted by a constituent element of the accelerator other than these magnets to change the tune of the charged particles.

Beam Energy/Intensity

M. Yanagisawa, et. al. “Charged Particle Therapy System, Range Modulation Wheel Device, and Method of Installing Range Modulation Wheel Device”, U.S. Pat. No. 7,355,189 (Apr. 8, 2008) and Yanagisawa, et. al. “Charged Particle Therapy System, Range Modulation Wheel Device, and Method of Installing Range Modulation Wheel Device”, U.S. Pat. No. 7,053,389 (May 30, 2008) both describe a particle therapy system having a range modulation wheel. The ion beam passes through the range modulation wheel resulting in a plurality of energy levels corresponding to a plurality of stepped thicknesses of the range modulation wheel.

M. Yanagisawa, et. al. “Particle Beam Irradiation System and Method of Adjusting Irradiation Apparatus”, U.S. Pat. No. 7,297,967 (Nov. 20, 2007); M. Yanagisawa, et. al. “Particle Beam Irradiation System and Method of Adjusting Irradiation Apparatus”, U.S. Pat. No. 7,071,479 (Jul. 4, 2006); M. Yanagisawa, et. al. “Particle Beam Irradiation System and Method of Adjusting Irradiation Apparatus”, U.S. Pat. No. 7,026,636 (Apr. 11, 2006); and M. Yanagisawa, et. al. “Particle Beam Irradiation System and Method of Adjusting Irradiation Apparatus”, U.S. Pat. No. 6,777,700 (Aug. 17, 2004) all describe a scattering device, a range adjustment device, and a peak spreading device. The scattering device and range adjustment device are combined together and are moved along a beam axis. The spreading device is independently moved along the axis to adjust the degree of ion beam scattering. The combined device increases the degree of uniformity of radiation dose distribution to diseased tissue.

A. Sliski, et. al. “Programmable Particle Scatterer for Radiation Therapy Beam Formation”, U.S. Pat. No. 7,208,748 (Apr. 24, 2007) describe a programmable pathlength of a fluid disposed into a particle beam to modulate scattering angle and beam range in a predetermined manner. The charged particle beam scatterer/range modulator comprises a fluid reservoir having opposing walls in a particle beam path and a drive to adjust the distance between the walls of the fluid reservoir under control of a programmable controller to create a predetermined spread out Bragg peak at a predetermined depth in a tissue. The beam scattering and modulation is continuously and dynamically adjusted during treatment of a tumor to deposit a dose in a targeted predetermined three dimensional volume.

M. Tadokoro, et. al. “Particle Therapy System”, U.S. Pat. No. 7,247,869 (Jul. 24, 2007) and U.S. Pat. No. 7,154,108 (Dec. 26, 2006) each describe a particle therapy system capable of measuring energy of a charged particle beam during irradiation of cancerous tissue. The system includes a beam passage between a pair of collimators, an energy detector, and a signal processing unit.

G. Kraft, et. al. “Ion Beam Scanner System and Operating Method”, U.S. Pat. No. 6,891,177 (May 10, 2005) describe an ion beam scanning system having a mechanical alignment system for the target volume to be scanned allowing for depth modulation of the ion beam by means of a linear motor and transverse displacement of energy absorption means resulting in depth-staggered scanning of volume elements of a target volume.

G. Hartmann, et. al. “Method for Operating an Ion Beam Therapy System by Monitoring the Distribution of the Radiation Dose”, U.S. Pat. No. 6,736,831 (May 18, 2004) describe a method for operation of an ion beam therapy system having a grid scanner that irradiates and scans an area surrounding an isocentre. Both the depth dose distribution and the transverse dose distribution of the grid scanner device at various positions in the region of the isocentre are measured and evaluated.

Y. Jongen “Method for Treating a Target Volume with a Particle Beam and Device Implementing Same”, U.S. Pat. No. 6,717,162 (Apr. 6, 2004) describes a method of producing from a particle beam a narrow spot directed toward a target volume, characterized in that the spot sweeping speed and particle beam intensity are simultaneously varied.

G. Kraft, et. al. “Device for Irradiating a Tumor Tissue”, U.S. Pat. No. 6,710,362 (Mar. 23, 2004) describe a method and apparatus of irradiating a tumor tissue, where the apparatus has an electromagnetically driven ion-braking device in the proton beam path for depth-wise adaptation of the proton beam that adjusts both the ion beam direction and ion beam range.

K. Matsuda, et. al. “Charged Particle Beam Irradiation Apparatus”, U.S. Pat. No. 6,617,598 (Sep. 9, 2003) describe a charged particle beam irradiation apparatus that increases the width in a depth direction of a Bragg peak by passing the Bragg peak through an enlarging device containing three ion beam components having different energies produced according to the difference between passed positions of each of the filter elements.

H. Stelzer, et. al. “Ionization Chamber for Ion Beams and Method for Monitoring the Intensity of an Ion Beam”, U.S. Pat. No. 6,437,513 (Aug. 20, 2002) describe an ionization chamber for ion beams and a method of monitoring the intensity of an ion therapy beam. The ionization chamber includes a chamber housing, a beam inlet window, a beam outlet window and a chamber volume filled with counting gas.

H. Akiyama, et. al. “Charged-Particle Beam Irradiation Method and System”, U.S. Pat. No. 6,433,349 (Aug. 13, 2002) and H. Akiyama, et. al. “Charged-Particle Beam Irradiation Method and System”, U.S. Pat. No. 6,265,837 (Jul. 24, 2001) both describe a charged particle beam irradiation system that includes a changer for changing energy of the particle and an intensity controller for controlling an intensity of the charged-particle beam.

Y. Pu “Charged Particle Beam Irradiation Apparatus and Method of Irradiation with Charged Particle Beam”, U.S. Pat. No. 6,034,377 (Mar. 7, 2000) describes a charged particle beam irradiation apparatus having an energy degrader comprising: (1) a cylindrical member having a length; and (2) a distribution of wall thickness in a circumferential direction around an axis of rotation, where thickness of the wall determines energy degradation of the irradiation beam.

Gantry

T. Yamashita, et. al. “Rotating Irradiation Apparatus”, U.S. Pat. No. 7,381,979 (Jun. 3, 2008) describe a rotating gantry having a front ring and a rear ring, each ring having radial support devices, where the radial support devices have linear guides. The system has thrust support devices for limiting movement of the rotatable body in the direction of the rotational axis of the rotatable body.

T. Yamashita, et. al. “Rotating Gantry of Particle Beam Therapy System” U.S. Pat. No. 7,372,053 (May 13, 2008) describe a rotating gantry supported by an air braking system allowing quick movement, braking, and stopping of the gantry during irradiation treatment.

M. Yanagisawa, et. al. “Medical Charged Particle Irradiation Apparatus”, U.S. Pat. No. 6,992,312 (Jan. 31, 2006); M. Yanagisawa, et. al. “Medical Charged Particle Irradiation Apparatus”, U.S. Pat. No. 6,979,832 (Dec. 27, 2005); and M. Yanagisawa, et. al. “Medical Charged Particle Irradiation Apparatus”, U.S. Pat. No. 6,953,943 (Oct. 11, 2005) all describe an apparatus capable of irradiation from upward and horizontal directions. The gantry is rotatable about an axis of rotation where the irradiation field forming device is eccentrically arranged, such that an axis of irradiation passes through a different position than the axis of rotation.

H. Kaercher, et. al. “Isokinetic Gantry Arrangement for the Isocentric Guidance of a Particle Beam And a Method for Constructing Same”, U.S. Pat. No. 6,897,451 (May 24, 2005) describe an isokinetic gantry arrangement for isocentric guidance of a particle beam that can be rotated around a horizontal longitudinal axis.

G. Kraft, et. al. “Ion Beam System for Irradiating Tumor Tissues”, U.S. Pat. No. 6,730,921 (May 4, 2004) describe an ion beam system for irradiating tumor tissues at various irradiation angles in relation to a horizontally arranged patient couch, where the patient couch is rotatable about a center axis and has a lifting mechanism. The system has a central ion beam deflection of up to ±15 degrees with respect to a horizontal direction.

M. Pavlovic, et. al. “Gantry System and Method for Operating Same”, U.S. Pat. No. 6,635,882 (Oct. 21, 2003) describe a gantry system for adjusting and aligning an ion beam onto a target from a freely determinable effective treatment angle. The ion beam is aligned on a target at adjustable angles of from 0 to 360 degrees around the gantry rotation axis and at an angle of 45 to 90 degrees off of the gantry rotation axis yielding a cone of irradiation when rotated a full revolution about the gantry rotation axis.

Respiration

K. Matsuda “Radioactive Beam Irradiation Method and Apparatus Taking Movement of the Irradiation Area Into Consideration”, U.S. Pat. No. 5,538,494 (Jul. 23, 1996) describes a method and apparatus that enables irradiation even in the case of a diseased part changing position due to physical activity, such as breathing and heart beat. Initially, a position change of a diseased body part and physical activity of the patient are measured concurrently and a relationship therebetween is defined as a function. Radiation therapy is performed in accordance to the function.

Patient Positioning

Y. Nagamine, et. al. “Patient Positioning Device and Patient Positioning Method”, U.S. Pat. No. 7,212,609 (May 1, 2007) and Y. Nagamine, et. al. “Patient Positioning Device and Patient Positioning Method”, U.S. Pat. No. 7,212,608 (May 1, 2007) describe a patient positioning system that compares a comparison area of a reference X-ray image and a current X-ray image of a current patient location using pattern matching.

D. Miller, et. al. “Modular Patient Support System”, U.S. Pat. No. 7,173,265 (Feb. 6, 2007) describe a radiation treatment system having a patient support system that includes a modularly expandable patient pod and at least one immobilization device, such as a moldable foam cradle.

K. Kato, et. al. “Multi-Leaf Collimator and Medical System Including Accelerator”, U.S. Pat. No. 6,931,100 (Aug. 16, 2005); K. Kato, et. al. “Multi-Leaf Collimator and Medical System Including Accelerator”, U.S. Pat. No. 6,823,045 (Nov. 23, 2004); K. Kato, et. al. “Multi-Leaf Collimator and Medical System Including Accelerator”, U.S. Pat. No. 6,819,743 (Nov. 16, 2004); and K. Kato, et. al. “Multi-Leaf Collimator and Medical System Including Accelerator”, U.S. Pat. No. 6,792,078 (Sep. 14, 2004) all describe a system of leaf plates used to shorten positioning time of a patient for irradiation therapy. Motor driving force is transmitted to a plurality of leaf plates at the same time through a pinion gear. The system also uses upper and lower air cylinders and upper and lower guides to position a patient.

Problem

There exists in the art of particle beam therapy of cancerous tumors a need for an integrated charged particle cancer therapy system, which is preferably compact, cost effective, accurate, and precise.

SUMMARY OF THE INVENTION

The invention comprises a charged particle beam path integrated into a charged particle cancer therapy method and apparatus.

DESCRIPTION OF THE FIGURES

FIG. 1 illustrates component connections of a particle beam therapy system;

FIG. 2 illustrates a charged particle therapy system;

FIG. 3 illustrates an ion beam generation system;

FIG. 4 illustrates straight and turning sections of a synchrotron;

FIG. 5 illustrates bending magnets of a synchrotron;

FIG. 6 provides a perspective view of a bending magnet;

FIG. 7 illustrates a cross-sectional view of a bending magnet;

FIG. 8 illustrates a cross-sectional view of a bending magnet;

FIG. 9 illustrates a magnetic turning section of a synchrotron;

FIGS. 10A and B illustrate an RF accelerator and an RF accelerator subsystem, respectively;

FIG. 11 illustrates a magnetic field control system;

FIG. 12 illustrates a charged particle extraction and intensity control system;

FIG. 13 illustrates a proton beam position verification system;

FIG. 14 illustrates a patient positioning system from: (A) a front view and (B) a top view;

FIG. 15 provides X-ray and proton beam dose distributions;

FIGS. 16 A-E illustrate controlled depth of focus irradiation;

FIGS. 17 A-E illustrate multi-field irradiation;

FIG. 18 illustrates dose efficiency enhancement via use of multi-field irradiation;

FIG. 19 provides two methods of multi-field irradiation implementation;

FIG. 20 illustrates multi-dimensional scanning of a charged particle beam spot scanning system operating on: (A) a 2-D slice or (B) a 3-D volume of a tumor;

FIG. 21 illustrates an electron gun source used in generating X-rays coupled with a particle beam therapy system;

FIG. 22 illustrates an X-ray source proximate a particle beam path;

FIG. 23 illustrates an expanded X-ray beam path;

FIG. 24 provides an X-ray tomography system;

FIG. 25 illustrates a semi-vertical patient positioning system; and

FIG. 26 provides a method of coordinating X-ray collection with patient breathing.

DETAILED DESCRIPTION OF THE INVENTION

The invention comprises a charged particle beam path integrated into a charged particle beam radiation method and apparatus for irradiation of tumors of a patient.

In one embodiment, the system comprises a charged particle beam path, through which charged particles flow. The charged particle beam path couples an injector, synchrotron accelerator, beam transport system, targeting system, and/or patient interface method and apparatus.

In another embodiment, the method and apparatus comprises a charged particle beam path coupling an injector, synchrotron accelerator, beam transport system, targeting system, and/or patient interface method and apparatus used to irradiate a tumor of a patient. Preferably, the injector comprises: a negative ion beam source, a two phase ion source vacuum system, an ion beam focusing lens, and/or a tandem accelerator. Preferably, the synchrotron comprises turning magnets, edge focusing magnets, magnetic field concentration magnets, winding and correction coils, flat magnetic field incident surfaces, and/or extraction elements. Preferably, the beam transport system, targeting system, and patient interface combine to allow multi-axis/multi-field irradiation, where multi-axis control comprises control of horizontal and vertical beam position, beam energy, and beam intensity and multi-field control comprises control of patient rotation and distribution of delivered energy in and about the tumor in a time controlled, targeted, accurate, precise, dosage controlled, and efficient manner. In one example, the charged particle beam path begins at the injector and ends in the tumor or above the rotatable platform holding the patients. In another example, the charged particle beam path passes over the rotatable platform holding the patient. In still another example, the charged particle beam path circumferentially surrounds the negative ion beam in the injector, the circulating charged particles in the synchrotron, spans the charged particle beam path in the extraction step, or is proximate the charged particle beam path in the transport system from the synchrotron to the tumor. In still yet another example, the charged particle beam comprises the walls of the gap through which the protons travel. In yet still another example, the charged particle beam path passes proximate to the X-ray generation source. Permutations and combinations of the charged particle beam path include beam path surrounding any of the apparatus components described herein.

Used in combination with the method and apparatus, novel design features of a charged particle beam cancer therapy system are optionally used. Particularly, a negative ion beam source with novel features in the negative ion source, ion source vacuum system, ion beam focusing lens, and tandem accelerator is described. Additionally, synchrotron turning magnets, edge focusing magnets, magnetic field concentration magnets, winding and correction coils, flat magnetic field incident surfaces, and extraction elements are described that minimize the overall size of the synchrotron, provide a tightly controlled proton beam, directly reduce the size of required magnetic fields, directly reduce required operating power, and allow continual acceleration of protons in a synchrotron even during a process of extracting protons from the synchrotron. The ion beam source system and synchrotron are preferably computer integrated with a patient imaging system and a patient interface including respiration monitoring sensors and patient positioning elements. Further, intensity control of a charged particle beam acceleration, extraction, and/or targeting method and apparatus used in conjunction with charged particle beam radiation therapy of cancerous tumors is described. More particularly, intensity, energy, and timing control of a charged particle stream of a synchrotron is described. The synchrotron control elements allow tight control of the charged particle beam, which compliments the tight control of patient positioning to yield efficient treatment of a solid tumor with reduced tissue damage to surrounding healthy tissue. In addition, the system reduces the overall size of the synchrotron, provides a tightly controlled proton beam, directly reduces the size of required magnetic fields, directly reduces required operating power, and allows continual acceleration of protons in a synchrotron even during a process of extracting protons from the synchrotron. All of these systems are preferably used in conjunction with an X-ray system capable of collecting X-rays of a patient in (1) a positioning system for proton treatment and (2) at a specified moment of the patient's respiration cycle. Combined, the systems provide for efficient, accurate, and precise noninvasive tumor treatment with minimal damage to surrounding healthy tissue.

Charged Particle Beam Therapy

Throughout this document, a charged particle beam therapy system, such as a proton beam, hydrogen ion beam, or carbon ion beam, is described. Herein, the charged particle beam therapy system is described using a proton beam. However, the aspects taught and described in terms of a proton beam are not intended to be limiting to that of a proton beam and are illustrative of a charged particle beam system. Any charged particle beam system is equally applicable to the techniques described herein.

Referring now to FIG. 1, a charged particle beam system 100 is illustrated. The charged particle beam preferably comprises a number of subsystems including any of: a main controller 110; an injection system 120; a synchrotron 130 that typically includes: (1) an accelerator system 132 and (2) an extraction system 134; a scanning/targeting/delivery system 140; a patient interface module 150; a display system 160; and/or an imaging system 170.

An exemplary method of use of the charged particle beam system 100 is provided. The main controller 110 controls one or more of the subsystems to accurately and precisely deliver protons to a tumor of a patient. For example, the main controller 110 obtains an image, such as a portion of a body and/or of a tumor, from the imaging system 170. The main controller 110 also obtains position and/or timing information from the patient interface module 150. The main controller 110 then optionally controls the injection system 120 to inject a proton into a synchrotron 130. The synchrotron typically contains at least an accelerator system 132 and an extraction system 134. The main controller preferably controls the proton beam within the accelerator system, such as by controlling speed, trajectory, and timing of the proton beam. The main controller then controls extraction of a proton beam from the accelerator through the extraction system 134. For example, the controller controls timing, energy, and/or intensity of the extracted beam. The controller 110 also preferably controls targeting of the proton beam through the scanning/targeting/delivery system 140 to the patient interface module 150. One or more components of the patient interface module 150 are preferably controlled by the main controller 110. Further, display elements of the display system 160 are preferably controlled via the main controller 110. Displays, such as display screens, are typically provided to one or more operators and/or to one or more patients. In one embodiment, the main controller 110 times the delivery of the proton beam from all systems, such that protons are delivered in an optimal therapeutic manner to the patient.

Herein, the main controller 110 refers to a single system controlling the charged particle beam system 100, to a single controller controlling a plurality of subsystems controlling the charged particle beam system 100, or to a plurality of individual controllers controlling one or more sub-systems of the charged particle beam system 100.

Synchrotron

Herein, the term synchrotron is used to refer to a system maintaining the charged particle beam in a circulating path; however, cyclotrons are alternatively used, albeit with their inherent limitations of energy, intensity, and extraction control. Further, the charged particle beam is referred to herein as circulating along a circulating path about a central point of the synchrotron. The circulating path is alternatively referred to as an orbiting path; however, the orbiting path does not refer a perfect circle or ellipse, rather it refers to cycling of the protons around a central point or region.

Referring now to FIG. 2, an illustrative exemplary embodiment of one version of the charged particle beam system 100 is provided. The number, position, and described type of components is illustrative and non-limiting in nature. In the illustrated embodiment, an injector system 210 or ion source or charged particle beam source generates protons. The protons are delivered into a vacuum tube that runs into, through, and out of the synchrotron. The generated protons are delivered along an initial path 262. Focusing magnets 230, such as quadrupole magnets or injection quadrupole magnets, are used to focus the proton beam path. A quadrupole magnet is a focusing magnet. An injector bending magnet 232 bends the proton beam toward the plane of the synchrotron 130. The focused protons having an initial energy are introduced into an injector magnet 240, which is preferably an injection Lamberson magnet. Typically, the initial beam path 262 is along an axis off of, such as above, a circulating plane of the synchrotron 130. The injector bending magnet 232 and injector magnet 240 combine to move the protons into the synchrotron 130. Main bending magnets 250 or dipole magnets or circulating magnets are used to turn the protons along a circulating beam path 264. A dipole magnet is a bending magnet. The main bending magnets 250 bend the initial beam path 262 into a circulating beam path 264. In this example, the main bending magnets 250 or circulating magnets are represented as four sets of four magnets to maintain the circulating beam path 264 into a stable circulating beam path. However, any number of magnets or sets of magnets are optionally used to move the protons around a single orbit in the circulation process. The protons pass through an accelerator 270. The accelerator accelerates the protons in the circulating beam path 264. As the protons are accelerated, the fields applied by the magnets are increased. Particularly, the speed of the protons achieved by the accelerator 270 are synchronized with magnetic fields of the main bending magnets 250 or circulating magnets to maintain stable circulation of the protons about a central point or region 280 of the synchrotron. At separate points in time the accelerator 270/main bending magnet 250 combination is used to accelerate and/or decelerate the circulating protons while maintaining the protons in the circulating path or orbit. An extraction element of the inflector/deflector system 290 is used in combination with a Lamberson extraction magnet 292 to remove protons from their circulating beam path 264 within the synchrotron 130. One example of a deflector component is a Lamberson magnet. Typically the deflector moves the protons from the circulating plane to an axis off of the circulating plane, such as above the circulating plane. Extracted protons are preferably directed and/or focused using an extraction bending magnet 237 and extraction focusing magnets 235, such as quadrupole magnets along a transport path 268 into the scanning/targeting/delivery system 140. Two components of a scanning system 140 or targeting system typically include a first axis control 142, such as a vertical control, and a second axis control 144, such as a horizontal control. In one embodiment, the first axis control 142 allows for about 100 mm of vertical scanning of the proton beam 268 and the second axis control 144 allows for about 700 mm of horizontal scanning of the proton beam 268. A nozzle system 146 is used for imaging the proton beam and/or as a vacuum barrier between the low pressure beam path of the synchrotron and the atmosphere. Protons are delivered with control to the patient interface module 150 and to a tumor of a patient. All of the above listed elements are optional and may be used in various permutations and combinations.

Ion Beam Generation System

An ion beam generation system generates a negative ion beam, such as a hydrogen anion or H⁻ beam; preferably focuses the negative ion beam; converts the negative ion beam to a positive ion beam, such as a proton or H⁺ beam; and injects the positive ion beam into the synchrotron 130. Portions of the ion beam path are preferably under partial vacuum. Each of these systems are further described, infra.

Referring now to FIG. 3, an exemplary ion beam generation system 300 is illustrated. As illustrated, the ion beam generation system 300 has four major elements: a negative ion source 310, a first partial vacuum system 330, an optional ion beam focusing system 350, and a tandem accelerator 390.

Still referring to FIG. 3, the negative ion source 310 preferably includes an inlet port 312 for injection of hydrogen gas into a high temperature plasma chamber 314. In one embodiment, the plasma chamber includes a magnetic material 316, which provides a magnetic field barrier 317 between the high temperature plasma chamber 314 and a low temperature plasma region on the opposite side of the magnetic field barrier. An extraction pulse is applied to a negative ion extraction electrode 318 to pull the negative ion beam into a negative ion beam path 319, which proceeds through the first partial vacuum system 330, through the ion beam focusing system 350, and into the tandem accelerator 390.

Still referring to FIG. 3, the first partial vacuum system 330 is an enclosed system running from the hydrogen gas inlet port 312 to the tandem accelerator 390 input foil 395. The input foil 395 is sealed directly or indirectly to the edges of the vacuum tube 320 providing for a higher pressure, such as about 10⁻⁵ torr, to be maintained on the first partial vacuum system 330 side of the foil 395 and a lower pressure, such as about 10⁻⁷ torr, to be maintained on the synchrotron side of the foil 390. By only pumping first partial vacuum system 330 and by only semi-continuously operating the ion beam source vacuum based on sensor readings, the lifetime of the semi-continuously operating pump is extended. The sensor readings are further described, infra.

Still referring to FIG. 3, the first partial vacuum system 330 preferably includes: a first pump 332, such as a continuously operating pump and/or a turbo molecular pump; a large holding volume 334; and a semi-continuously operating pump 336. Preferably, a pump controller 340 receives a signal from a pressure sensor 342 monitoring pressure in the large holding volume 334. Upon a signal representative of a sufficient pressure in the large holding volume 334, the pump controller 340 instructs an actuator 345 to open a valve 346 between the large holding volume and the semi-continuously operating pump 336 and instructs the semi-continuously operating pump to turn on and pump to atmosphere residual gases out of the vacuum line 320 about the charged particle stream. In this fashion, the lifetime of the semi-continuously operating pump is extended by only operating semi-continuously and as needed. In one example, the semi-continuously operating pump 336 operates for a few minutes every few hours, such as 5 minutes every 4 hours, thereby extending a pump with a lifetime of about 2,000 hours to about 96,000 hours.

Further, by isolating the inlet gas from the synchrotron vacuum system, the synchrotron vacuum pumps, such as turbo molecular pumps can operate over a longer lifetime as the synchrotron vacuum pumps have fewer gas molecules to deal with. For example, the inlet gas is primarily hydrogen gas but may contain impurities, such as nitrogen and carbon dioxide. By isolating the inlet gases in the negative ion source system 310, first partial vacuum system 330, ion beam focusing system 350 and negative ion beam side of the tandem accelerator 390, the synchrotron vacuum pumps can operate at lower pressures with longer lifetimes, which increases the efficiency of the synchrotron 130.

Still referring to FIG. 3, the ion beam focusing system 350 includes two or more electrodes where one electrode of each electrode pair partially obstructs the ion beam path with conductive paths 372, such as a conductive mesh. In the illustrated example, three ion beam focusing system sections are illustrated, a two electrode ion focusing section 360, a first three electrode ion focusing section 370, and a second three electrode ion focusing section 380. In a given electrode pair, electric field lines, running between the conductive mesh of a first electrode and a second electrode, provide inward forces focusing the negative ion beam. Multiple such electrode pairs provide multiple negative ion beam focusing regions. Preferably the two electrode ion focusing section 360, first three electrode ion focusing section 370, and second three electrode ion focusing section 380 are placed after the negative ion source and before the tandem accelerator and/or cover a space of about 0.5, 1, or 2 meters along the ion beam path. Ion beam focusing systems are further described, infra.

Still referring to FIG. 3, the tandem accelerator 390 preferably includes a foil 395, such as a carbon foil. The negative ions in the negative ion beam path 319 are converted to positive ions, such as protons, and the initial ion beam path 262 results. The foil 395 is preferably sealed directly or indirectly to the edges of the vacuum tube 320 providing for a higher pressure, such as about 10⁻⁵ torr, to be maintained on the side of the foil 395 having the negative ion beam path 319 and a lower pressure, such as about 10⁻⁷ torr, to be maintained on the side of the foil 390 having the proton ion beam path 262. Having the foil 395 physically separating the vacuum chamber 320 into two pressure regions allows for a system having fewer and/or smaller pumps to maintain the lower pressure system in the synchrotron 130 as the inlet hydrogen and its residuals are extracted in a separate contained and isolated space by the first partial vacuum system 330.

Referring again to FIG. 1, another exemplary method of use of the charged particle beam system 100 is provided. The main controller 110, or one or more sub-controllers, controls one or more of the subsystems to accurately and precisely deliver protons to a tumor of a patient. For example, the main controller sends a message to the patient indicating when or how to breath. The main controller 110 obtains a sensor reading from the patient interface module, such as a temperature breath sensor or a force reading indicative of where in a breath cycle the subject is. The main controller collects an image, such as a portion of a body and/or of a tumor, from the imaging system 170. The main controller 110 also obtains position and/or timing information from the patient interface module 150. The main controller 110 then optionally controls the injection system 120 to inject hydrogen gas into a negative ion beam source 310 and controls timing of extraction of the negative ion from the negative ion beam source 310. Optionally, the main controller controls ion beam focusing the ion beam focusing lens system 350; acceleration of the proton beam with the tandem accelerator 390; and/or injection of the proton into the synchrotron 130. The synchrotron typically contains at least an accelerator system 132 and an extraction system 134. The synchrotron preferably contains one or more of: turning magnets, edge focusing magnets, magnetic field concentration magnets, winding and correction coils, and flat magnetic field incident surfaces, some of which contain elements under control by the main controller 110. The main controller preferably controls the proton beam within the accelerator system, such as by controlling speed, trajectory, and/or timing of the proton beam. The main controller then controls extraction of a proton beam from the accelerator through the extraction system 134. For example, the controller controls timing, energy, and/or intensity of the extracted beam. The controller 110 also preferably controls targeting of the proton beam through the targeting/delivery system 140 to the patient interface module 150. One or more components of the patient interface module 150 are preferably controlled by the main controller 110, such as vertical position of the patient, rotational position of the patient, and patient chair positioning/stabilization/control elements. Further, display elements of the display system 160 are preferably controlled via the main controller 110. Displays, such as display screens, are typically provided to one or more operators and/or to one or more patients. In one embodiment, the main controller 110 times the delivery of the proton beam from all systems, such that protons are delivered in an optimal therapeutic manner to the patient.

Circulating System

A synchrotron 130 preferably comprises a combination of straight sections 410 and ion beam turning sections 420. Hence, the circulating path of the protons is not circular in a synchrotron, but is rather a polygon with rounded corners.

In one illustrative embodiment, the synchrotron 130, which as also referred to as an accelerator system, has four straight elements and four turning sections. Examples of straight sections 410 include the: inflector 240, accelerator 270, extraction system 290, and deflector 292. Along with the four straight sections are four ion beam turning sections 420, which are also referred to as magnet sections or turning sections. Turning sections are further described, infra.

Referring now to FIG. 4, an exemplary synchrotron is illustrated. In this example, protons delivered along the initial proton beam path 262 are inflected into the circulating beam path with the inflector 240 and after acceleration are extracted via a deflector 292 to a beam transport path 268. In this example, the synchrotron 130 comprises four straight sections 410 and four bending or turning sections 420 where each of the four turning sections use one or more magnets to turn the proton beam about ninety degrees. As is further described, infra, the ability to closely space the turning sections and efficiently turn the proton beam results in shorter straight sections. Shorter straight sections allows for a synchrotron design without the use of focusing quadrupoles in the circulating beam path of the synchrotron. The removal of the focusing quadrupoles from the circulating proton beam path results in a more compact design. In this example, the illustrated synchrotron has about a five meter diameter versus eight meter and larger cross-sectional diameters for systems using a quadrupole focusing magnet in the circulating proton beam path.

Referring now to FIG. 5, additional description of the first bending or turning section 420 is provided. Each of the turning sections preferably comprises multiple magnets, such as about 2, 4, 6, 8, 10, or 12 magnets. In this example, four turning magnets 510, 520, 530, 540 in the first turning section 420 are used to illustrate key principles, which are the same regardless of the number of magnets in a turning section 420. A turning magnet 510 is a particular type of main bending or circulating magnet 250.

In physics, the Lorentz force is the force on a point charge due to electromagnetic fields. The Lorentz force is given by equation 1 in terms of magnetic fields with the election field terms not included.

F=q(v×B)  eq. 1

In equation 1, F is the force in newtons; B is the magnetic field in Teslas; and v is the instantaneous velocity of the particles in meters per second.

Referring now to FIG. 6, an example of a single magnet bending or turning section 510 is expanded. The turning section includes a gap 610 through which protons circulate. The gap 610 is preferably a flat gap, allowing for a magnetic field across the gap 610 that is more uniform, even, and intense. A magnetic field enters the gap 610 through a magnetic field incident surface and exits the gap 610 through a magnetic field exiting surface. The gap 610 runs in a vacuum tube between two magnet halves. The gap 610 is controlled by at least two parameters: (1) the gap 610 is kept as large as possible to minimize loss of protons and (2) the gap 610 is kept as small as possible to minimize magnet sizes and the associated size and power requirements of the magnet power supplies. The flat nature of the gap 610 allows for a compressed and more uniform magnetic field across the gap 610. One example of a gap dimension is to accommodate a vertical proton beam size of about 2 cm with a horizontal beam size of about 5 to 6 cm.

As described, supra, a larger gap size requires a larger power supply. For instance, if the gap 610 size doubles in vertical size, then the power supply requirements increase by about a factor of 4. The flatness of the gap 610 is also important. For example, the flat nature of the gap 610 allows for an increase in energy of the extracted protons from about 250 to about 330 MeV. More particularly, if the gap 610 has an extremely flat surface, then the limits of a magnetic field of an iron magnet are reachable. An exemplary precision of the flat surface of the gap 610 is a polish of less than about 5 microns and preferably with a polish of about 1 to 3 microns. Unevenness in the surface results in imperfections in the applied magnetic field. The polished flat surface spreads unevenness of the applied magnetic field.

Still referring to FIG. 6, the charged particle beam moves through the gap 610 with an instantaneous velocity, v. A first magnetic coil 620 and a second magnetic coil 630 run above and below the gap 610, respectively. Current running through the coils 620, 630 results in a magnetic field, B, running through the single magnet turning section 510. In this example, the magnetic field, B, runs upward, which results in a force, F, pushing the charged particle beam inward toward a central point of the synchrotron, which turns the charged particle beam in an arc.

Still referring to FIG. 6, a portion of an optional second magnet bending or turning section 520 is illustrated. The coils 620, 630 typically have return elements 640, 650 or turns at the end of one magnet, such as at the end of the first magnet turning section 510. The turns 640, 650 take space. The space reduces the percentage of the path about one orbit of the synchrotron that is covered by the turning magnets. This leads to portions of the circulating path where the protons are not turned and/or focused and allows for portions of the circulating path where the proton path defocuses. Thus, the space results in a larger synchrotron. Therefore, the space between magnet turning sections 660 is preferably minimized. The second turning magnet is used to illustrate that the coils 620, 630 optionally run along a plurality of magnets, such as 2, 3, 4, 5, 6, or more magnets. Coils 620, 630 running across multiple turning section magnets allows for two turning section magnets to be spatially positioned closer to each other due to the removal of the steric constraint of the turns, which reduces and/or minimizes the space 660 between two turning section magnets.

Referring now to FIGS. 7 and 8, two illustrative 90 degree rotated cross-sections of single magnet bending or turning sections 510 are presented. Referring now to FIG. 8, the magnet assembly has a first magnet 810 and a second magnet 820. A magnetic field induced by coils, described infra, runs between the first magnet 810 to the second magnet 820 across the gap 610. Return magnetic fields run through a first yoke 812 and second yoke 822. The combined cross-section area of the return yokes roughly approximates the cross-sectional area of the first magnet 810 or second magnet 820. The charged particles run through the vacuum tube in the gap 610. As illustrated, protons run into FIG. 8 through the gap 610 and the magnetic field, illustrated as vector B, applies a force F to the protons pushing the protons towards the center of the synchrotron, which is off page to the right in FIG. 8. The magnetic field is created using windings. A first coil makes up a first winding coil 850 and a second coil of wire makes up a second winding coil 860. Isolating or concentrating gaps 830, 840, such as air gaps, isolate the iron based yokes from the gap 610. The gap 610 is approximately flat to yield a uniform magnetic field across the gap 610, as described supra.

Still again to FIG. 7, the ends of a single bending or turning magnet are preferably beveled. Nearly perpendicular or right angle edges of a turning magnet 510 are represented by dashed lines 774, 784. The dashed lines 774, 784 intersect at a point 790 beyond the center of the synchrotron 280. Preferably, the edge of the turning magnet is beveled at angles alpha, α, and beta, β, which are angles formed by a first line 772, 782 going from an edge of the turning magnet 510 and the center 280 and a second line 774, 784 going from the same edge of the turning magnet and the intersecting point 790. The angle alpha is used to describe the effect and the description of angle alpha applies to angle beta, but angle alpha is optionally different from angle beta. The angle alpha provides an edge focusing effect. Beveling the edge of the turning magnet 510 at angle alpha focuses the proton beam.

Multiple turning magnets provide multiple magnet edges that each have edge focusing effects in the synchrotron 130. If only one turning magnet is used, then the beam is only focused once for angle alpha or twice for angle alpha and angle beta. However, by using smaller turning magnets, more turning magnets fit into the turning sections 420 of the synchrotron 130. For example, if four magnets are used in a turning section 420 of the synchrotron, then for a single turning section there are eight possible edge focusing effect surfaces, two edges per magnet. The eight focusing surfaces yield a smaller cross-sectional beam size. This allows the use of a smaller gap 610.

The use of multiple edge focusing effects in the turning magnets results in not only a smaller gap 610, but also the use of smaller magnets and smaller power supplies. For a synchrotron 130 having four turning sections 420 where each turning sections has four turning magnets and each turning magnet has two focusing edges, a total of thirty-two focusing edges exist for each orbit of the protons in the circulating path of the synchrotron 130. Similarly, if 2, 6, or 8 magnets are used in a given turning section, or if 2, 3, 5, or 6 turning sections are used, then the number of edge focusing surfaces expands or contracts according to equation 2.

$\begin{matrix} {{TFE} = {{NTS}*\frac{M}{NTS}*\frac{FE}{M}}} & {{eq}.\mspace{14mu} 2} \end{matrix}$

where TFE is the number of total focusing edges, NTS is the number of turning sections, M is the number of magnets, and FE is the number of focusing edges. Naturally, not all magnets are necessarily beveled and some magnets are optionally beveled on only one edge.

The inventors have determined that multiple smaller magnets have benefits over fewer larger magnets. For example, the use of 16 small magnets yields 32 focusing edges whereas the use of 4 larger magnets yields only 8 focusing edges. The use of a synchrotron having more focusing edges results in a circulating path of the synchrotron built without the use of focusing quadrupoles magnets. All prior art synchrotrons use quadrupoles in the circulating path of the synchrotron. Further, the use of quadrupoles in the circulating path necessitates additional straight sections in the circulating path of the synchrotron. Thus, the use of quadrupoles in the circulating path of a synchrotron results in synchrotrons having larger diameters, circulating beam pathlengths, and/or larger circumferences.

In various embodiments of the system described herein, the synchrotron has any combination of:

-   -   at least 4 and preferably 6, 8, 10, or more edge focusing edges         per 90 degrees of turn of the charged particle beam in a         synchrotron having four turning sections;     -   at least about 16 and preferably about 24, 32, or more edge         focusing edges per orbit of the charged particle beam in the         synchrotron;     -   only 4 turning sections where each of the turning sections         includes at least 4 and preferably 8 edge focusing edges;     -   an equal number of straight sections and turning sections;     -   exactly 4 turning sections;     -   at least 4 edge focusing edges per turning section;     -   no quadrupoles in the circulating path of the synchrotron;     -   a rounded corner rectangular polygon configuration;     -   a circumference of less than 60 meters;     -   a circumference of less than 60 meters and 32 edge focusing         surfaces; and/or     -   any of about 8, 16, 24, or 32 non-quadrupole magnets per         circulating path of the synchrotron, where the non-quadrupole         magnets include edge focusing edges.

Referring again to FIG. 8, the incident magnetic field surface 870 of the first magnet 810 is further described. FIG. 8 is not to scale and is illustrative in nature. Local imperfections or unevenness in quality of the finish of the incident surface 870 results in inhomogeneities or imperfections in the magnetic field applied to the gap 610. Preferably, the incident surface 870 is flat, such as to within about a zero to three micron finish polish, or less preferably to about a ten micron finish polish.

Referring still to FIG. 8, additional magnet elements are described. The first magnet 810 preferably contains an initial cross sectional distance 890 of the iron based core. The contours of the magnetic field are shaped by the magnets 810, 820 and the yokes 812, 822. The iron based core tapers to a second cross sectional distance 892. The magnetic field in the magnet preferentially stays in the iron based core as opposed to the gaps 830, 840. As the cross-sectional distance decreases from the initial cross sectional distance 890 to the final cross-sectional distance 892, the magnetic field concentrates. The change in shape of the magnet from the longer distance 890 to the smaller distance 892 acts as an amplifier. The concentration of the magnetic field is illustrated by representing an initial density of magnetic field vectors 894 in the initial cross section 890 to a concentrated density of magnetic field vectors 896 in the final cross section 892. The concentration of the magnetic field due to the geometry of the turning magnets results in fewer winding coils 850, 860 being required and also a smaller power supply to the coils being required.

In one example, the initial cross-section distance 890 is about fifteen centimeters and the final cross-section distance 892 is about ten centimeters. Using the provided numbers, the concentration of the magnetic field is about 15/10 or 1.5 times at the incident surface 870 of the gap 610, though the relationship is not linear. The taper 842 has a slope, such as about 20, 40, or 60 degrees. The concentration of the magnetic field, such as by 1.5 times, leads to a corresponding decrease in power consumption requirements to the magnets.

Referring still to FIG. 8, the first magnet 810 preferably contains an initial cross sectional distance 890 of the iron based core. The contours of the magnetic field are shaped by the magnets 810, 820 and the yokes 812, 822. In this example, the core tapers to a second cross sectional distance 892 with a smaller angle theta, θ. As described, supra, the magnetic field in the magnet preferentially stays in the iron based core as opposed to the gaps 830, 840. As the cross-sectional distance decreases from the initial cross sectional distance 890 to the final cross-sectional distance 892, the magnetic field concentrates. The smaller angle, theta, results in a greater amplification of the magnetic field in going from the longer distance 890 to the smaller distance 892. The concentration of the magnetic field is illustrated by representing an initial density of magnetic field vectors 894 in the initial cross section 890 to a concentrated density of magnetic field vectors 896 in the final cross section 892. The concentration of the magnetic field due to the geometry of the turning magnets results in fewer winding coils 850, 860 being required and also a smaller power supply to the winding coils 850, 860 being required.

Still referring to FIG. 8, optional correction coils 852, 862 are illustrated that are used to correct the strength of one or more turning magnets. The correction coils 852, 862 supplement the winding coils 850, 860. The correction coils 852, 862 have correction coil power supplies that are separate from winding coil power supplies used with the winding coils 850, 860. The correction coil power supplies typically operate at a fraction of the power required compared to the winding coil power supplies, such as about 1, 2, 3, 5, 7, or 10 percent of the power and more preferably about 1 or 2 percent of the power used with the winding coils 850, 860. The smaller operating power applied to the correction coils 852, 862 allows for more accurate and/or precise control of the correction coils. Correction coils are used to adjust for imperfection in the turning magnets 510, 520, 530, 540. Optionally, separate correction coils are used for each turning magnet allowing individual tuning of the magnetic field for each turning magnet, which eases quality requirements in the manufacture of each turning magnet.

Referring now to FIG. 9, an example of winding coils and correction coils about a plurality of turning magnets 510, 520, 530, 540 in an ion beam turning section 420 is illustrated. One or more high precision magnetic field sensors are placed into the synchrotron and are used to measure the magnetic field at or near the proton beam path. For example, the magnetic sensors 950 are optionally placed between turning magnets and/or within a turning magnet, such as at or near the gap 610 or at or near the magnet core or yoke. The sensors are part of a feedback system to the correction coils. Thus, the system preferably stabilizes the magnetic field in the synchrotron elements rather that stabilizing the current applied to the magnets. Stabilization of the magnetic field allows the synchrotron to come to a new energy level quickly. This allows the system to be controlled to an operator or algorithm selected energy level with each pulse of the synchrotron and/or with each breath of the patient.

The winding and/or correction coils correct 1, 2, 3, or 4 turning magnets, and preferably correct a magnetic field generated by two turning magnets. A winding or correction coil covering multiple magnets reduces space between magnets as fewer winding or correction coil ends are required, which occupy space.

Referring now to FIG. 10A and FIG. 10B, the accelerator system 270, such as a radio-frequency (RF) accelerator system, is further described. The accelerator includes a series of coils 1010-1019, such as iron or ferrite coils, each circumferentially enclosing the vacuum system 320 through which the proton beam 264 passes in the synchrotron 130. Referring now to FIG. 10B, the first coil 1010 is further described. A loop of standard wire 1030 completes at least one turn about the first coil 1010. The loop attaches to a microcircuit 1020. Referring again to FIG. 10A, an RF synthesizer 1040, which is preferably connected to the main controller 110, provides a low voltage RF signal that is synchronized to the period of circulation of protons in the proton beam path 264. The RF synthesizer 1040, microcircuit 1020, loop 1030, and coil 1010 combine to provide an accelerating voltage to the protons in the proton beam path 264. For example, the RF synthesizer 1040 sends a signal to the microcircuit 1020, which amplifies the low voltage RF signal and yields an acceleration voltage, such as about 10 volts. The actual acceleration voltage for a single microcircuit/loop/coil combination is about 5, 10, 15, or 20 volts, but is preferably about 10 volts. Preferably, the RF-amplifier microcircuit and accelerating coil are integrated.

Still referring to FIG. 10A, the integrated RF-amplifier microcircuit and accelerating coil presented in FIG. 10B is repeated, as illustrated as the set of coils 1011-1019 surrounding the vacuum tube 320. For example, the RF-synthesizer 1040, under main controller 130 direction, sends an RF-signal to the microcircuits 1020-1029 connected to coils 1010-1019, respectively. Each of the microcircuit/loop/coil combinations generates a proton accelerating voltage, such as about 10 volts each. Hence, a set of five coil combinations generates about 50 volts for proton acceleration. Preferably about 5 to 20 microcircuit/loop/coil combinations are used and more preferably about 9 or 10 microcircuit/loop/coil combinations are used in the accelerator system 270.

As a further clarifying example, the RF synthesizer 1040 sends an RF-signal, with a period equal to a period of circulation of a proton about the synchrotron 130, to a set of ten microcircuit/loop/coil combinations, which results in about 100 volts for acceleration of the protons in the proton beam path 264. The 100 volts is generated at a range of frequencies, such as at about 1 MHz for a low energy proton beam to about 15 MHz for a high energy proton beam. The RF-signal is optionally set at an integer multiple of a period of circulation of the proton about the synchrotron circulating path. Each of the microcircuit/loop/coil combinations are optionally independently controlled in terms of acceleration voltage and frequency.

Integration of the RF-amplifier microcircuit and accelerating coil, in each microcircuit/loop/coil combination, results in three considerable advantages. First, for synchrotrons, the prior art does not use microcircuits integrated with the accelerating coils but rather uses a set of long cables to provide power to a corresponding set of coils. The long cables have an impedance/resistance, which is problematic for high frequency RF control. As a result, the prior art system is not operable at high frequencies, such as above about 10 MHz. The integrated RF-amplifier microcircuit/accelerating coil system is operable at above about 10 MHz and even 15 MHz where the impedance and/or resistance of the long cables in the prior art systems results in poor control or failure in proton acceleration. Second, the long cable system, operating at lower frequencies, costs about $50,000 and the integrated microcircuit system costs about $1000, which is 50 times less expensive. Third, the microcircuit/loop/coil combinations in conjunction with the RF-amplifier system results in a compact low power consumption design allowing production and use of a proton cancer therapy system is a small space, as described supra, and in a cost effective manner.

Referring now to FIG. 11, an example is used to clarify the magnetic field control using a feedback loop 1100 to change delivery times and/or periods of proton pulse delivery. In one case, a respiratory sensor 1110 senses the breathing cycle of the subject. The respiratory sensor sends the information to an algorithm in a magnetic field controller 1120, typically via the patient interface module 150 and/or via the main controller 110 or a subcomponent thereof. The algorithm predicts and/or measures when the subject is at a particular point in the breathing cycle, such as at the bottom of a breath. Magnetic field sensors 1130 are used as input to the magnetic field controller, which controls a magnet power supply 1140 for a given magnetic field 1150, such as within a first turning magnet 510 of a synchrotron 130. The control feedback loop is thus used to dial the synchrotron to a selected energy level and deliver protons with the desired energy at a selected point in time, such as at the bottom of the breath. More particularly, the main controller injects protons into the synchrotron and accelerates the protons in a manner that combined with extraction delivers the protons to the tumor at a selected point in the breathing cycle. Intensity of the proton beam is also selectable and controllable by the main controller at this stage. The feedback control to the correction coils allows rapid selection of energy levels of the synchrotron that are tied to the patient's breathing cycle. This system is in stark contrast to a system where the current is stabilized and the synchrotron deliver pulses with a period, such as 10 or 20 cycles per second with a fixed period. Optionally, the feedback or the magnetic field design coupled with the correction coils allows for the extraction cycle to match the varying respiratory rate of the patient.

Traditional extraction systems do not allow this control as magnets have memories in terms of both magnitude and amplitude of a sine wave. Hence, in a traditional system, in order to change frequency, slow changes in current must be used. However, with the use of the feedback loop using the magnetic field sensors, the frequency and energy level of the synchrotron are rapidly adjustable. Further aiding this process is the use of a novel extraction system that allows for acceleration of the protons during the extraction process, described infra.

Example III

Referring again to FIG. 9, an example of a winding coil 930 that covers two turning magnets 510, 520 is provided. Optionally, a first winding coil 940 covers one magnets or a second winding coil 920 covers a plurality of magnets 510, 520. As described, supra, this system reduces space between turning section allowing more magnetic field to be applied per radian of turn. A first correction coil 910 is illustrated that is used to correct the magnetic field for the first turning magnet 510. A second correction coil 920 is illustrated that is used to correct the magnetic field for a winding coil 930 about two turning magnets. Individual correction coils for each turning magnet are preferred and individual correction coils yield the most precise and/or accurate magnetic field in each turning section. Particularly, the individual correction coil 910 is used to compensate for imperfections in the individual magnet of a given turning section. Hence, with a series of magnetic field sensors, corresponding magnetic fields are individually adjustable in a series of feedback loops, via a magnetic field monitoring system, as an independent coil is used for each turning section. Alternatively, a multiple magnet correction coil is used to correct the magnetic field for a plurality of turning section magnets.

Flat Gap Surface

While the gap surface is described in terms of the first turning magnet 510, the discussion applies to each of the turning magnets in the synchrotron. Similarly, while the gap 610 surface is described in terms of the magnetic field incident surface 670, the discussion additionally optionally applies to the magnetic field exiting surface 680.

The magnetic field incident surface 870 of the first magnet 810 is preferably about flat, such as to within about a zero to three micron finish polish or less preferably to about a ten micron finish polish. By being very flat, the polished surface spreads the unevenness of the applied magnetic field across the gap 610. The very flat surface, such as about 0, 1, 2, 4, 6, 8, 10, 15, or 20 micron finish, allows for a smaller gap size, a smaller applied magnetic field, smaller power supplies, and tighter control of the proton beam cross-sectional area. The magnetic field exiting surface 880 is also preferably flat.

Proton Beam Extraction

Referring now to FIG. 12, an exemplary proton extraction process from the synchrotron 130 is illustrated. For clarity, FIG. 12 removes elements represented in FIG. 2, such as the turning magnets, which allows for greater clarity of presentation of the proton beam path as a function of time. Generally, protons are extracted from the synchrotron 130 by slowing the protons. As described, supra, the protons were initially accelerated in a circulating path 264, which is maintained with a plurality of main bending magnets 250. The circulating path is referred to herein as an original central beamline 264. The protons repeatedly cycle around a central point in the synchrotron 280. The proton path traverses through a radio frequency (RF) cavity system 1210. To initiate extraction, an RF field is applied across a first blade 1212 and a second blade 1214, in the RF cavity system 1210. The first blade 1212 and second blade 1214 are referred to herein as a first pair of blades.

In the proton extraction process, an RF voltage is applied across the first pair of blades, where the first blade 1212 of the first pair of blades is on one side of the circulating proton beam path 264 and the second blade 1214 of the first pair of blades is on an opposite side of the circulating proton beam path 264. The applied RF field applies energy to the circulating charged-particle beam. The applied RF field alters the orbiting or circulating beam path slightly of the protons from the original central beamline 264 to an altered circulating beam path 265. Upon a second pass of the protons through the RF cavity system, the RF field further moves the protons off of the original proton beamline 264. For example, if the original beamline is considered as a circular path, then the altered beamline is slightly elliptical. The applied RF field is timed to apply outward or inward movement to a given band of protons circulating in the synchrotron accelerator. Each orbit of the protons is slightly more off axis compared to the original circulating beam path 264. Successive passes of the protons through the RF cavity system are forced further and further from the original central beamline 264 by altering the direction and/or intensity of the RF field with each successive pass of the proton beam through the RF field.

The RF voltage is frequency modulated at a frequency about equal to the period of one proton cycling around the synchrotron for one revolution or at a frequency than is an integral multiplier of the period of one proton cycling about the synchrotron. The applied RF frequency modulated voltage excites a betatron oscillation. For example, the oscillation is a sine wave motion of the protons. The process of timing the RF field to a given proton beam within the RF cavity system is repeated thousands of times with each successive pass of the protons being moved approximately one micrometer further off of the original central beamline 264. For clarity, the approximately 1000 changing beam paths with each successive path of a given band of protons through the RF field are illustrated as the altered beam path 265.

With a sufficient sine wave betatron amplitude, the altered circulating beam path 265 touches a material 1230, such as a foil an extraction foil, an extraction material or a sheet of foil. The foil is preferably a lightweight material, such as beryllium, a lithium hydride, a carbon sheet, or a material of low nuclear charge. A material of low nuclear charge is a material composed of atoms consisting essentially of atoms having six or fewer protons. The foil is preferably about 10 to 150 microns thick, is more preferably 30 to 100 microns thick, and is still more preferably 40-60 microns thick. In one example, the foil is beryllium with a thickness of about 50 microns. When the protons traverse through the foil, energy of the protons is lost and the speed of the protons is reduced. Typically, a current is also generated, described infra. Protons moving at a slower speed travel in the synchrotron with a reduced radius of curvature 266 compared to either the original central beamline 264 or the altered circulating path 265. The reduced radius of curvature 266 path is also referred to herein as a path having a smaller diameter of trajectory or a path having protons with reduced energy. The reduced radius of curvature 266 is typically about two millimeters less than a radius of curvature of the last pass of the protons along the altered proton beam path 265.

The thickness of the material 1230 is optionally adjusted to created a change in the radius of curvature, such as about ½, 1, 2, 3, or 4 mm less than the last pass of the protons 265 or original radius of curvature 264. Protons moving with the smaller radius of curvature travel between a second pair of blades. In one case, the second pair of blades is physically distinct and/or are separated from the first pair of blades. In a second case, one of the first pair of blades is also a member of the second pair of blades. For example, the second pair of blades is the second blade 1214 and a third blade 1216 in the RF cavity system 1210. A high voltage DC signal, such as about 1 to 5 kV, is then applied across the second pair of blades, which directs the protons out of the synchrotron through an extraction magnet 292, such as a Lamberson extraction magnet, into a transport path 268.

Control of acceleration of the charged particle beam path in the synchrotron with the accelerator and/or applied fields of the turning magnets in combination with the above described extraction system allows for control of the intensity of the extracted proton beam, where intensity is a proton flux per unit time or the number of protons extracted as a function of time. For example, when a current is measured beyond a threshold, the RF field modulation in the RF cavity system is terminated or reinitiated to establish a subsequent cycle of proton beam extraction. This process is repeated to yield many cycles of proton beam extraction from the synchrotron accelerator.

Because the extraction system does not depend on any change in magnetic field properties, it allows the synchrotron to continue to operate in acceleration or deceleration mode during the extraction process. Stated differently, the extraction process does not interfere with synchrotron acceleration. In stark contrast, traditional extraction systems introduce a new magnetic field, such as via a hexapole, during the extraction process. More particularly, traditional synchrotrons have a magnet, such as a hexapole magnet, that is off during an acceleration stage. During the extraction phase, the hexapole magnetic field is introduced to the circulating path of the synchrotron. The introduction of the magnetic field necessitates two distinct modes, an acceleration mode and an extraction mode, which are mutually exclusive in time.

Charged Particle Beam Intensity Control

Control of applied field, such as a radio-frequency (RF) field, frequency and magnitude in the RF cavity system 1210 allows for intensity control of the extracted proton beam, where intensity is extracted proton flux per unit time or the number of protons extracted as a function of time.

Referring still to FIG. 12, when protons in the proton beam hit the material 1230 electrons are given off resulting in a current. The resulting current is converted to a voltage and is used as part of a ion beam intensity monitoring system or as part of an ion beam feedback loop for controlling beam intensity. The voltage is optionally measured and sent to the main controller 110 or to a controller subsystem. More particularly, when protons in the charged particle beam path pass through the material 1230, some of the protons lose a small fraction of their energy, such as about one-tenth of a percent, which results in a secondary electron. That is, protons in the charged particle beam push some electrons when passing through material 1230 giving the electrons enough energy to cause secondary emission. The resulting electron flow results in a current or signal that is proportional to the number of protons going through the target material 1230. The resulting current is preferably converted to voltage and amplified. The resulting signal is referred to as a measured intensity signal.

The amplified signal or measured intensity signal resulting from the protons passing through the material 1230 is preferably used in controlling the intensity of the extracted protons. For example, the measured intensity signal is compared to a goal signal, which is predetermined in an irradiation of the tumor plan 1260. In one example, the tumor plan 1260 contains the goal or targeted energy and intensity of the delivered proton beam as a function of x-position, y-position, time, and/or rotational position of the patient. The difference between the measured intensity signal and the planned for goal signal is calculated. The difference is used as a control to the RF generator. Hence, the measured flow of current resulting from the protons passing through the material 1230 is used as a control in the RF generator to increase or decrease the number of protons undergoing betatron oscillation and striking the material 1230. Hence, the voltage determined off of the material 1230 is used as a measure of the orbital path and is used as a feedback control to control the RF cavity system. Alternatively, the measured intensity signal is not used in the feedback control and is just used as a monitor of the intensity of the extracted protons.

As described, supra, the photons striking the material 1230 is a step in the extraction of the protons from the synchrotron 130. Hence, the measured intensity signal is used to change the number of protons per unit time being extracted, which is referred to as intensity of the proton beam. The intensity of the proton beam is thus under algorithm control. Further, the intensity of the proton beam is controlled separately from the velocity of the protons in the synchrotron 130. Hence, intensity of the protons extracted and the energy of the protons extracted are independently variable.

For example, protons initially move at an equilibrium trajectory in the synchrotron 130. An RF field is used to excite the protons into a betatron oscillation. In one case, the frequency of the protons orbit is about 10 MHz. In one example, in about one millisecond or after about 10,000 orbits, the first protons hit an outer edge of the target material 130. The specific frequency is dependent upon the period of the orbit. Upon hitting the material 130, the protons push electrons through the foil to produce a current. The current is converted to voltage and amplified to yield a measured intensity signal. The measured intensity signal is used as a feedback input to control the applied RF magnitude, RF frequency, or RF field. Preferably, the measured intensity signal is compared to a target signal and a measure of the difference between the measured intensity signal and target signal is used to adjust the applied RF field in the RF cavity system 1210 in the extraction system to control the intensity of the protons in the extraction step. Stated again, the signal resulting from the protons striking and/or passing through the material 130 is used as an input in RF field modulation. An increase in the magnitude of the RF modulation results in protons hitting the foil or material 130 sooner. By increasing the RF, more protons are pushed into the foil, which results in an increased intensity, or more protons per unit time, of protons extracted from the synchrotron 130.

In another example, a detector 1250 external to the synchrotron 130 is used to determine the flux of protons extracted from the synchrotron and a signal from the external detector is used to alter the RF field or RF modulation in the RF cavity system 1210. Here the external detector generates an external signal, which is used in a manner similar to the measured intensity signal, described in the preceding paragraphs. Particularly, the measured intensity signal is compared to a desired signal from the irradiation plan 1260 in a feedback intensity controller 1240, which adjusts the RF field between the first plate 1212 and the second plate 1214 in the extraction process, described supra.

In yet another example, when a current from material 130 resulting from protons passing through or hitting material is measured beyond a threshold, the RF field modulation in the RF cavity system is terminated or reinitiated to establish a subsequent cycle of proton beam extraction. This process is repeated to yield many cycles of proton beam extraction from the synchrotron accelerator.

In still yet another embodiment, intensity modulation of the extracted proton beam is controlled by the main controller 110. The main controller 110 optionally and/or additionally controls timing of extraction of the charged particle beam and energy of the extracted proton beam.

The benefits of the system include a multi-dimensional scanning system. Particularly, the system allows independence in: (1) energy of the protons extracted and (2) intensity of the protons extracted. That is, energy of the protons extracted is controlled by an energy control system and an intensity control system controls the intensity of the extracted protons. The energy control system and intensity control system are optionally independently controlled. Preferably, the main controller 110 controls the energy control system and the main controller simultaneously controls the intensity control system to yield an extracted proton beam with controlled energy and controlled intensity where the controlled energy and controlled intensity are independently variable. Thus the irradiation spot hitting the tumor is under independent control of:

-   -   time;     -   energy;     -   intensity;     -   x-axis position, where the x-axis represents horizontal movement         of the proton beam relative to the patient, and     -   y-axis position, where the y-axis represents vertical movement         of the proton beam relative to the patient.

In addition, the patient is optionally independently rotated relative to a translational axis of the proton beam at the same time. The system is capable of pulse-to-pulse energy variability. Additionally, the system is capable of dynamic energy modulation during a pulse, enabling true three-dimensional proton beam scanning with energy and/or intensity modulation.

Referring now to FIG. 13, a proton beam position verification system 1300 is described. A nozzle 1310 provides an outlet for the second reduced pressure vacuum system initiating at the foil 395 of the tandem accelerator 390 and running through the synchrotron 130 to a nozzle foil 1320 covering the end of the nozzle 1310. The nozzle expands in cross-sectional area along the z-axis of the proton beam path 268 to allow the proton beam 268 to be scanned along the x- and y-axes by the vertical control element 142 and horizontal control element 144, respectively. The nozzle foil 1320 is preferably mechanically supported by the outer edges of an exit port of the nozzle 1310. An example of a nozzle foil or output foil 1320 is a sheet of about 0.1 inch thick aluminum foil. Generally, the nozzle foil separates atmosphere pressures on the patient side of the nozzle foil 1320 from the low pressure region, such as about 10⁻⁵ to 10⁻⁷ torr region, on the synchrotron 130 side of the nozzle foil 1320. The low pressure region is maintained to reduce scattering of the proton beam 264, 268.

Still referring to FIG. 13, the proton beam verification system 1300 is a system that allows for monitoring of the actual proton beam position 268, 269 in real-time without destruction of the proton beam. The proton beam verification system 1300 preferably includes a proton beam position verification layer 1330, which is also referred to herein as a coating, luminescent, fluorescent, phosphorescent, radiance, or viewing layer. The verification layer or coating layer 1330 is preferably a coating or thin layer substantially in contact with an inside surface of the nozzle foil or output foil 1320, where the inside surface is on the synchrotron side of the nozzle foil 1320. Less preferably, the verification layer or coating layer 1330 is substantially in contact with an outer surface of the nozzle foil 1320, where the outer surface is on the patient treatment side of the nozzle foil 1320. Preferably, the nozzle foil 1320 provides a substrate surface for coating by the coating layer, but optionally a separate coating layer support element, on which the coating 1330 is mounted, is placed anywhere in the proton beam path 268. The coating layer preferably contains protons emitting centers or molecular structures that emit photons when struck by charged particles, such as protons.

Still referring to FIG. 13, the coating 1330 yields a measurable spectroscopic response, spatially viewable by the detector 1340, as a result of transmission by the proton beam 268. The coating 1330 is preferably a phosphor, but is optionally any material that is viewable or imaged by a detector where the material changes spectroscopically as a result of the proton beam path 268 hitting or transmitting through the coating 1330. For example, the coating 1330 emits photons when struck by charged particles in the charged particle beam path. A detector or camera 1340 views the coating layer 1330 and determines the current position of the proton beam 268 by the spectroscopic differences resulting from protons passing through the coating layer. For example, the camera 1340 views the coating surface 1330 as the proton beam 268 is being scanned by the horizontal 144 and vertical 142 beam position control elements during treatment of the tumor 1420. The camera 1340 views the current position of the proton beam 268 as measured by spectroscopic response. The coating layer 1330 is preferably a phosphor or luminescent material that glows or emits photons for a short period of time, such as less than 5 seconds for a 50% intensity, as a result of excitation by the proton beam 268. Optionally, a plurality of cameras or detectors 1340 are used, where each detector views all or a portion of the coating layer 1330. For example, two detectors 1340 are used where a first detector views a first half of the coating layer and the second detector views a second half of the coating layer. Preferably, the detector 1340 is mounted into the nozzle 1310 to view the proton beam position after passing through the first axis and second axis controllers 142, 144. Preferably, the coating layer 1330 is positioned in the proton beam path 268 in a position prior to the protons striking the patient 1430.

Still referring to FIG. 13, the main controller 130, connected to the camera or detector 1340 output, compares the actual proton beam position 268 with the planned proton beam position and/or a calibration reference to determine if the actual proton beam position 268 is within tolerance. The proton beam verification system 1300 preferably is used in at least two phases, a calibration phase and a proton beam treatment phase. The calibration phase is used to correlate, as a function of x-, y-position of the glowing response the actual x-, y-position of the proton beam at the patient interface. During the proton beam treatment phase, the proton beam position is monitored and compared to the calibration and/or treatment plan to verify accurate proton delivery to the tumor 1420 and/or as a proton beam shutoff safety indicator.

Patient Positioning

Referring now to FIG. 14, the patient is preferably positioned on or within a patient positioning system 1410 of the patient interface module 150. The patient positioning system 1410 is used to translate the patient and/or rotate the patient into a zone where the proton beam can scan the tumor using a scanning system 140 or proton targeting system, described infra. Essentially, the patient positioning system 1410 performs large movements of the patient to place the tumor near the center of a proton beam path 268 and the proton scanning or targeting system 140 performs fine movements of the momentary beam position 269 in targeting the tumor 1420. To illustrate, FIG. 14 shows the momentary proton beam position 269 and a range of scannable positions 1440 using the proton scanning or targeting system 140, where the scannable positions 1440 are about the tumor 1420 of the patient 1430. In this example, the scannable positions are scanned along the x- and y-axes; however, scanning is optionally simultaneously performed along the z-axis as described infra. This illustratively shows that the y-axis movement of the patient occurs on a scale of the body, such as adjustment of about 1, 2, 3, or 4 feet, while the scannable region of the proton beam 268 covers a portion of the body, such as a region of about 1, 2, 4, 6, 8, 10, or 12 inches. The patient positioning system and its rotation and/or translation of the patient combines with the proton targeting system to yield precise and/or accurate delivery of the protons to the tumor.

Referring still to FIG. 14, the patient positioning system 1410 optionally includes a bottom unit 1412 and a top unit 1414, such as discs or a platform. Referring now to FIG. 14A, the patient positioning unit 1410 is preferably y-axis adjustable 1416 to allow vertical shifting of the patient relative to the proton therapy beam 268. Preferably, the vertical motion of the patient positioning unit 1410 is about 10, 20, 30, or 50 centimeters per minute. Referring now to FIG. 14B, the patient positioning unit 1410 is also preferably rotatable 1417 about a rotation axis, such as about the y-axis running through the center of the bottom unit 1412 or about a y-axis running through the tumor 1420, to allow rotational control and positioning of the patient relative to the proton beam path 268. Preferably the rotational motion of the patient positioning unit 1410 is about 360 degrees per minute. Optionally, the patient positioning unit rotates about 45, 90, or 180 degrees. Optionally, the patient positioning unit 1410 rotates at a rate of about 45, 90, 180, 360, 720, or 1080 degrees per minute. The rotation of the positioning unit 1417 is illustrated about the rotation axis at two distinct times, t₁ and t₂. Protons are optionally delivered to the tumor 1420 at n times where each of the n times represent different directions of the incident proton beam 269 hitting the patient 1430 due to rotation of the patient 1417 about the rotation axis.

Any of the semi-vertical, sitting, or laying patient positioning embodiments described, infra, are optionally vertically translatable along the y-axis or rotatable about the rotation or y-axis.

Preferably, the top and bottom units 1412, 1414 move together, such that they rotate at the same rates and translate in position at the same rates. Optionally, the top and bottom units 1412, 1414 are independently adjustable along the y-axis to allow a difference in distance between the top and bottom units 1412, 1414. Motors, power supplies, and mechanical assemblies for moving the top and bottom units 1412, 1414 are preferably located out of the proton beam path 269, such as below the bottom unit 1412 and/or above the top unit 1414. This is preferable as the patient positioning unit 1410 is preferably rotatable about 360 degrees and the motors, power supplies, and mechanical assemblies interfere with the protons if positioned in the proton beam path 269

Proton Delivery Efficiency

Referring now to FIG. 15, a common distribution of relative doses for both X-rays and proton irradiation is presented. As shown, X-rays deposit their highest dose near the surface of the targeted tissue and then exponentially decreases as function of tissue depth. The deposition of X-ray energy near the surface is non-ideal for tumors located deep within the body, which is usually the case, as excessive damage is done to the soft tissue layers surrounding the tumor 1420. The advantage of protons is that they deposit most of their energy near the end of the flight trajectory as the energy loss per unit path of the absorber transversed by a proton increases with decreasing particle velocity, giving rise to a sharp maximum in ionization near the end of the range, referred to herein as the Bragg peak. Furthermore, since the flight trajectory of the protons is variable by increasing or decreasing their initial kinetic energy or initial velocity, then the peak corresponding to maximum energy is movable within the tissue. Thus z-axis control of the proton depth of penetration is allowed by the acceleration/extraction process, described supra. As a result of the protons dose-distribution characteristics, a radiation oncologist can optimize dosage to the tumor 1420 while minimizing dosage to surrounding normal tissues.

The Bragg peak energy profile shows that protons deliver their energy across the entire length of the body penetrated by the proton up to a maximum penetration depth. As a result, energy is being delivered, in the distal portion of the Bragg peak energy profile, to healthy tissue, bone, and other body constituents before the proton beam hits the tumor. It follows that the shorter the pathlength in the body prior to the tumor, the higher the efficiency of proton delivery efficiency, where proton delivery efficiency is a measure of how much energy is delivered to the tumor relative to healthy portions of the patient. Examples of proton delivery efficiency include: (1) a ratio of proton energy delivered to the tumor over proton energy delivered to non-tumor tissue; (2) pathlength of protons in the tumor versus pathlength in the non-tumor tissue; and (3) damage to a tumor compared to damage to healthy body parts. Any of these measures are optionally weighted by damage to sensitive tissue, such as a nervous system element, heart, brain, or other organ. To illustrate, for a patient in a laying position where the patient is rotated about the y-axis during treatment, a tumor near the heart would at times be treated with protons running through the head-to-heart path, leg-to-heart path, or hip-to-heart path, which are all inefficient compared to a patient in a sitting or semi-vertical position where the protons are all delivered through a shorter chest-to-heart; side-of-body-to-heart, or back-to-heart path. Particularly, compared to a laying position, using a sitting or semi-vertical position of the patient, a shorter pathlength through the body to a tumor is provided to a tumor located in the torso or head, which results in a higher or better proton delivery efficiency.

Herein proton delivery efficiency is separately described from the time efficiency or synchrotron use efficiency, which is a fraction of time that the charged particle beam apparatus is in operation.

Depth Targeting

Referring now to FIGS. 16 A-E, x-axis scanning of the proton beam is illustrated while z-axis energy of the proton beam undergoes controlled variation 1600 to allow irradiation of slices of the tumor 1420. For clarity of presentation, the simultaneous y-axis scanning that is performed is not illustrated. In FIG. 16A, irradiation is commencing with the momentary proton beam position 269 at the start of a first slice. Referring now to FIG. 16B, the momentary proton beam position is at the end of the first slice. Importantly, during a given slice of irradiation, the proton beam energy is preferably continuously controlled and changed according to the tissue density in front of the tumor 1420. The variation of the proton beam energy to account for tissue density thus allows the beam stopping point, or Bragg peak, to remain inside the tissue slice. The variation of the proton beam energy during scanning is possible due to the acceleration/extraction techniques, described supra, which allow for acceleration of the proton beam during extraction. FIGS. 16C, 16D, and 16E show the momentary proton beam position in the middle of the second slice, two-thirds of the way through a third slice, and after finalizing irradiation from a given direction, respectively. Using this approach, controlled, accurate, and precise delivery of proton irradiation energy to the tumor 1420, to a designated tumor subsection, or to a tumor layer is achieved. Efficiency of deposition of proton energy to tumor, as defined as the ratio of the proton irradiation energy delivered to the tumor relative to the proton irradiation energy delivered to the healthy tissue is further described infra.

Multi-Field Irradiation

It is desirable to maximize efficiency of deposition of protons to the tumor 1420, as defined by maximizing the ratio of the proton irradiation energy delivered to the tumor 1420 relative to the proton irradiation energy delivered to the healthy tissue. Irradiation from one, two, or three directions into the body, such as by rotating the body about 90 degrees between irradiation sub-sessions results in proton irradiation from the distal portion of the Bragg peak concentrating into one, two, or three healthy tissue volumes, respectively. It is desirable to further distribute the distal portion of the Bragg peak energy evenly through the healthy volume tissue surrounding the tumor 1420.

Multi-field irradiation is proton beam irradiation from a plurality of entry points into the body. For example, the patient 1430 is rotated and the radiation source point is held constant. For example, as the patient 1430 is rotated through 360 degrees and proton therapy is applied from a multitude of angles resulting in the distal radiation being circumferentially spread about the tumor yielding enhanced proton irradiation efficiency. In one case, the body is rotated into greater than 3, 5, 10, 15, 20, 25, 30, or 35 positions and proton irradiation occurs with each rotation position. Rotation of the patient for proton therapy or for X-ray imaging is preferably about 45, 90, 135, 180, 270, or 360 degrees. Rotation of the patient is preferably performed using the patient positioning system 1410 and/or the bottom unit 1412 or disc, described supra. Rotation of the patient 1430 while keeping the delivery proton beam 268 in a relatively fixed orientation allows irradiation of the tumor 1420 from multiple directions without use of a new collimator for each direction. Further, as no new setup is required for each rotation position of the patient 1430, the system allows the tumor 1420 to be treated from multiple directions without reseating or positioning the patient, thereby minimizing tumor 1420 regeneration time and increasing patient 1430 cancer therapy throughput.

The patient is optionally centered on the bottom unit 1412 or the tumor 1420 is optionally centered on the bottom unit 1412. If the patient is centered on the bottom unit 1412, then the first axis control element 142 and second axis control element 144 are programmed to compensate for the off central axis of rotation position variation of the tumor 1420.

Referring now to FIGS. 17 A-E, an example of multi-field irradiation 1700 is presented. In this example, five patient rotation positions are illustrated; however, the five rotation positions are discrete rotation positions of about thirty-six rotation positions, where the body is rotated about ten degrees with each position. Referring now to FIG. 17A, a range of irradiation beam positions 269 is illustrated from a first body rotation position, illustrated as the patient 1430 facing the proton irradiation beam where a first healthy volume 1711 is irradiated by the ingress or distal portion of the Bragg peak energy irradiation profile. Referring now to FIG. 17B, the patient 1430 is rotated about forty degrees and the irradiation is repeated. In the second position, the tumor 1420 again receives the bulk of the irradiation energy and a second healthy tissue volume 1712 receives the smaller ingress or distal portion of the Bragg peak energy. Referring now to FIGS. 17 C-E, the patient 1430 is rotated a total of about 90, 130, and 180 degrees, respectively. For each of the third, fourth, and fifth rotation positions, the tumor 1420 receives the bulk of the irradiation energy and the third 1713, fourth 1714, and fifth 1715 healthy tissue volumes receive the smaller ingress or distal portion of the Bragg peak energy, respectively. Thus, the rotation of the patient during proton therapy results in the distal energy of the delivered proton energy to be distributed about the tumor 1420, such as to regions one to five, while along a given axis, at least about 75, 80, 85, 90, or 95 percent of the energy is delivered to the tumor 1420.

For a given rotation position, all or part of the tumor is irradiated. For example, in one embodiment only a distal section or distal slice of the tumor 1420 is irradiated with each rotation position, where the distal section is a section furthest from the entry point of the proton beam into the patient 1430. For example, the distal section is the dorsal side of the tumor when the patient 1430 is facing the proton beam and the distal section is the ventral side of the tumor when the patient 1430 is facing away from the proton beam.

Referring now to FIG. 18, a second example of multi-field irradiation 1800 is presented where the proton source is stationary and the patient 1430 is rotated. For ease of presentation, the proton beam path 269 is illustrated as entering the patient 1430 from varying sides at times t₁, t₂, t₃, . . . , t_(n), t_(n+1). At a first time, t₁, the distal end of the Bragg peak profile hits a first area 1810, A₁. The patient is rotated and the proton beam path is illustrated at a second time, t₂, where the distal end of the Bragg peak hits a second area 1820, A₂. At a third time, the distal end of the Bragg peak profile hits a third area 1830, A₃. This rotation and irradiation process is repeated n times, where n is a positive number greater than four and preferably greater than about 10, 20, 30, 100, or 300. At an n^(th) time the distal end of the Bragg peak profile strikes an n^(th) area 1840. As illustrated, at an n^(th) time, t_(n), if the patient 1430 is rotated further, the proton beam would hit a sensitive body constituent 1450, such as the spinal cord or eyes. Irradiation is preferably suspended until the sensitive body constituent is rotated out of the proton beam path. Irradiation is resumed at a time, t_(n+1), after the sensitive body constituent 1450 is rotated our of the proton beam path. At time t_(n+1) the Bragg peak distal energy strikes a t_(n+1) area 1450. In this manner, the Bragg peak energy is always within the tumor, the distal region of the Bragg peak profile is distributed in healthy tissue about the tumor 1420, and sensitive body constituents 1450 receive minimal or no proton beam irradiation.

In one multi-field irradiation example, the particle therapy system with a synchrotron ring diameter of less than six meters includes ability to:

-   -   rotate the patient through about 360 degrees;     -   extract radiation in about 0.1 to 10 seconds;     -   scan vertically about 100 millimeters;     -   scan horizontally about 700 millimeters;     -   vary beam energy from about 30 to 330 MeV/second during         irradiation;     -   focus the proton beam from about 2 to 20 millimeters at the         tumor; and/or     -   complete multi-field irradiation of a tumor in less than about         1, 2, 4, or 6 minutes as measured from the time of initiating         proton delivery to the patient 1430.

Referring now to FIG. 19, two multi-field irradiation methods 1900 are described. In the first method, the main controller 110 rotationally positions 1910 the patient 1430 and subsequently irradiates 1920 the tumor 1420. The process is repeated until a multi-field irradiation plan is complete. In the second method, the main controller 110 simultaneously rotates and irradiates 1930 the tumor 1420 within the patient 1430 until the multi-field irradiation plan is complete. More particularly, the proton beam irradiation occurs while the patient 1430 is being rotated.

The 3-dimensional scanning system of the proton spot focal point, described herein, is preferably combined with a rotation/raster method. The method includes layer wise tumor irradiation from many directions. During a given irradiation slice, the proton beam energy is continuously changed according to the tissue's density in front of the tumor to result in the beam stopping point, defined by the Bragg peak, to always be inside the tumor and inside the irradiated slice. The novel method allows for irradiation from many directions, referred to herein as multi-field irradiation, to achieve the maximal effective dose at the tumor level while simultaneously significantly reducing possible side-effects on the surrounding healthy tissues in comparison with existing methods. Essentially, the multi-field irradiation system distributes dose-distribution at tissue depths not yet reaching the tumor.

Proton Beam Position Control

Referring now to FIG. 20, a beam delivery and tissue volume scanning system is illustrated. Presently, the worldwide radiotherapy community uses a method of dose field forming using a pencil beam scanning system. In stark contrast, FIG. 20 illustrates a spot scanning system or tissue volume scanning system. In the tissue volume scanning system, the proton beam is controlled, in terms of transportation and distribution, using an inexpensive and precise scanning system. The scanning system is an active system, where the beam is focused into a spot focal point of about one-half, one, two, or three millimeters in diameter. The focal point is translated along two axes while simultaneously altering the applied energy of the proton beam, which effectively changes the third dimension of the focal point. The system is applicable in combination with the above described rotation of the body, which preferably occurs in-between individual moments or cycles of proton delivery to the tumor. Optionally, the rotation of the body by the above described system occurs continuously and simultaneously with proton delivery to the tumor.

For example, in the illustrated system in FIG. 20A, the spot is translated horizontally, is moved down a vertical y-axis, and is then back along the horizontal axis. In this example, current is used to control a vertical scanning system having at least one magnet. The applied current alters the magnetic field of the vertical scanning system to control the vertical deflection of the proton beam. Similarly, a horizontal scanning magnet system controls the horizontal deflection of the proton beam. The degree of transport along each axes is controlled to conform to the tumor cross-section at the given depth. The depth is controlled by changing the energy of the proton beam. For example, the proton beam energy is decreased, so as to define a new penetration depth, and the scanning process is repeated along the horizontal and vertical axes covering a new cross-sectional area of the tumor. Combined, the three axes of control allow scanning or movement of the proton beam focal point over the entire volume of the cancerous tumor. The time at each spot and the direction into the body for each spot is controlled to yield the desired radiation does at each sub-volume of the cancerous volume while distributing energy hitting outside of the tumor.

The focused beam spot volume dimension is preferably tightly controlled to a diameter of about 0.5, 1, or 2 millimeters, but is alternatively several centimeters in diameter. Preferred design controls allow scanning in two directions with: (1) a vertical amplitude of about 100 mm amplitude and frequency up to about 200 Hz; and (2) a horizontal amplitude of about 700 mm amplitude and frequency up to about 1 Hz.

In FIG. 27A, the proton beam is illustrated along a z-axis controlled by the beam energy, the horizontal movement is along an x-axis, and the vertical direction is along a y-axis. The distance the protons move along the z-axis into the tissue, in this example, is controlled by the kinetic energy of the proton. This coordinate system is arbitrary and exemplary. The actual control of the proton beam is controlled in 3-dimensional space using two scanning magnet systems and by controlling the kinetic energy of the proton beam. The use of the extraction system, described supra, allows for different scanning patterns. Particularly, the system allows simultaneous adjustment of the x-, y-, and z-axes in the irradiation of the solid tumor. Stated again, instead of scanning along an x,y-plane and then adjusting energy of the protons, such as with a range modulation wheel, the system allows for moving along the z-axes while simultaneously adjusting the x- and or y-axes. Hence, rather than irradiating slices of the tumor, the tumor is optionally irradiated in three simultaneous dimensions. For example, the tumor is irradiated around an outer edge of the tumor in three dimensions. Then the tumor is irradiated around an outer edge of an internal section of the tumor. This process is repeated until the entire tumor is irradiated. The outer edge irradiation is preferably coupled with simultaneous rotation of the subject, such as about a vertical y-axis. This system allows for maximum efficiency of deposition of protons to the tumor, as defined as the ratio of the proton irradiation energy delivered to the tumor relative to the proton irradiation energy delivered to the healthy tissue.

Combined, the system allows for multi-axes control of the charged particle beam system in a small space with low power supply. For example, the system uses multiple magnets where each magnet has at least one edge focusing effect in each turning section of the synchrotron and/or multiple magnets having concentrating magnetic field geometry, as described supra. The multiple edge focusing effects in the circulating beam path of the synchrotron combined with the concentration geometry of the magnets and described extraction system yields a synchrotron having:

-   -   a small circumference system, such as less than about 50 meters;     -   a vertical proton beam size gap of about 2 cm;     -   corresponding reduced power supply requirements associated with         the reduced gap size;     -   an extraction system not requiring a newly introduced magnetic         field;     -   acceleration or deceleration of the protons during extraction;         and     -   control of z-axis energy during extraction.

The result is a 3-dimensional scanning system, x-, y-, and z-axes control, where the z-axes control resides in the synchrotron and where the z-axes energy is variably controlled during the extraction process inside the synchrotron.

Referring now to FIG. 27B, an example of a proton scanning or targeting system 140 used to direct the protons to the tumor with 4-dimensional scanning control is provided, where the 4-dimensional scanning control is along the x-, y-, and z-axes along with intensity control, as described supra. A fifth axis is time. Typically, charged particles traveling along the transport path 268 are directed through a first axis control element 142, such as a vertical control, and a second axis control element 144, such as a horizontal control and into a tumor 1420. As described, supra, the extraction system also allows for simultaneous variation in the z-axis. Further, as describe, supra, the intensity or dose of the extracted beam is optionally simultaneously and independently controlled and varied. Thus instead of irradiating a slice of the tumor, as in FIG. 27A, all four dimensions defining the targeting spot of the proton delivery in the tumor are simultaneously variable. The simultaneous variation of the proton delivery spot is illustrated in FIG. 27B by the spot delivery path 269. In the illustrated case, the protons are initially directed around an outer edge of the tumor and are then directed around an inner radius of the tumor. Combined with rotation of the subject about a vertical axis, a multi-field illumination process is used where a not yet irradiated portion of the tumor is preferably irradiated at the further distance of the tumor from the proton entry point into the body. This yields the greatest percentage of the proton delivery, as defined by the Bragg peak, into the tumor and minimizes damage to peripheral healthy tissue.

Imaging/X-Ray System

Herein, an X-ray system is used to illustrate an imaging system.

Timing

An X-ray is preferably collected either (1) just before or (2) concurrently with treating a subject with proton therapy for a couple of reasons. First, movement of the body, described supra, changes the local position of the tumor in the body relative to other body constituents. If the subject has an X-ray taken and is then bodily moved to a proton treatment room, accurate alignment of the proton beam to the tumor is problematic. Alignment of the proton beam to the tumor using one or more X-rays is best performed at the time of proton delivery or in the seconds or minutes immediately prior to proton delivery and after the patient is placed into a therapeutic body position, which is typically a fixed position or partially immobilized position. Second, the X-ray taken after positioning the patient is used for verification of proton beam alignment to a targeted position, such as a tumor and/or internal organ position.

Positioning

An X-ray is preferably taken just before treating the subject to aid in patient positioning. For positioning purposes, an X-ray of a large body area is not needed. In one embodiment, an X-ray of only a local area is collected. When collecting an X-ray, the X-ray has an X-ray path. The proton beam has a proton beam path. Overlaying the X-ray path with the proton beam path is one method of aligning the proton beam to the tumor. However, this method involves putting the X-ray equipment into the proton beam path, taking the X-ray, and then moving the X-ray equipment out of the beam path. This process takes time. The elapsed time while the X-ray equipment moves has a couple of detrimental effects. First, during the time required to move the X-ray equipment, the body moves. The resulting movement decreases precision and/or accuracy of subsequent proton beam alignment to the tumor. Second, the time required to move the X-ray equipment is time that the proton beam therapy system is not in use, which decreases the total efficiency of the proton beam therapy system.

X-Ray Source Lifetime

Preferably, components in the particle beam therapy system require minimal or no maintenance over the lifetime of the particle beam therapy system. For example, it is desirable to equip the proton beam therapy system with an X-ray system having a long lifetime source, such as a lifetime of about 20 years.

In one system, described infra, electrons are used to create X-rays. The electrons are generated at a cathode where the lifetime of the cathode is temperature dependent. Analogous to a light bulb, where the filament is kept in equilibrium, the cathode temperature is held in equilibrium at temperatures at about 200, 500, or 1000 degrees Celsius. Reduction of the cathode temperature results in increased lifetime of the cathode. Hence, the cathode used in generating the electrons is preferably held at as low of a temperature as possible. However, if the temperature of the cathode is reduced, then electron emissions also decrease. To overcome the need for more electrons at lower temperatures, a large cathode is used and the generated electrons are concentrated. The process is analogous to compressing electrons in an electron gun; however, here the compression techniques are adapted to apply to enhancing an X-ray tube lifetime.

Referring now to FIG. 21, an example of an X-ray generation device 2100 having an enhanced lifetime is provided. Electrons 2120 are generated at a cathode 2110, focused with a control electrode 2112, and accelerated with a series of accelerating electrodes 2140. The accelerated electrons 2150 impact an X-ray generation source 2148 resulting in generated X-rays that are then directed along an X-ray path 2270 to the subject 1430. The concentrating of the electrons from a first diameter 2115 to a second diameter 2116 allows the cathode to operate at a reduced temperature and still yield the necessary amplified level of electrons at the X-ray generation source 2148. In one example, the X-ray generation source is the anode coupled with the cathode 2110 and/or the X-ray generation source is substantially composed of tungsten.

Still referring to FIG. 21, a more detailed description of an exemplary X-ray generation device 2100 is described. An anode 2114/cathode 2110 pair is used to generated electrons. The electrons 2120 are generated at the cathode 2110 having a first diameter 2115, which is denoted d₁. The control electrodes 2112 attract the generated electrons 2120. For example, if the cathode is held at about −150 kV and the control electrode is held at about −149 kV, then the generated electrons 2120 are attracted toward the control electrodes 2112 and focused. A series of accelerating electrodes 2140 are then used to accelerate the electrons into a substantially parallel path 2150 with a smaller diameter 2116, which is denoted d₂. For example, with the cathode held at −150 kV, a first, second, third, and fourth accelerating electrodes 2142, 2144, 2146, 2148 are held at about −120, −90, −60, and −30 kV, respectively. If a thinner body part is to be analyzed, then the cathode 2110 is held at a smaller level, such as about −90 kV and the control electrode, first, second, third, and fourth electrode are each adjusted to lower levels. Generally, the voltage difference from the cathode to fourth electrode is less for a smaller negative voltage at the cathode and vise-versa. The accelerated electrons 2150 are optionally passed through a magnetic lens 2160 for adjustment of beam size, such as a cylindrical magnetic lens. The electrons are also optionally focused using quadrupole magnets 2170, which focus in one direction and defocus in another direction. The accelerated electrons 2150, which are now adjusted in beam size and focused strike an X-ray generation source 2148, such as tungsten, resulting in generated X-rays that pass through a blocker 2262 and proceed along an X-ray path 2170 to the subject. The X-ray generation source 2148 is optionally cooled with a cooling element 2149, such as water touching or thermally connected to a backside of the X-ray generation source 2148. The concentrating of the electrons from a first diameter 2115 to a second diameter 2116 allows the cathode to operate at a reduced temperature and still yield the necessary amplified level of electrons at the X-ray generation source 2148.

More generally, the X-ray generation device 2100 produces electrons having initial vectors. One or more of the control electrode 2112, accelerating electrodes 2140, magnetic lens 2160, and quadrupole magnets 2170 combine to alter the initial electron vectors into parallel vectors with a decreased cross-sectional area having a substantially parallel path, referred to as the accelerated electrons 2150. The process allows the X-ray generation device 2100 to operate at a lower temperature. Particularly, instead of using a cathode that is the size of the electron beam needed, a larger electrode is used and the resulting electrons 2120 are focused and/or concentrated into the required electron beam needed. As lifetime is roughly an inverse of current density, the concentration of the current density results in a larger lifetime of the X-ray generation device. A specific example is provided for clarity. If the cathode has a fifteen mm radius or d₁ is about 30 mm, then the area (π r²) is about 225 mm² times pi. If the concentration of the electrons achieves a radius of five mm or d₂ is about 10 mm, then the area (π r²) is about 25 mm² times pi. The ratio of the two areas is about nine (225π/25π). Thus, there is about nine times less density of current at the larger cathode compared to the traditional cathode having an area of the desired electron beam. Hence, the lifetime of the larger cathode approximates nine times the lifetime of the traditional cathode, though the actual current through the larger cathode and traditional cathode is about the same. Preferably, the area of the cathode 2110 is about 2, 4, 6, 8, 10, 15, 20, or 25 times that of the cross-sectional area of the substantially parallel electron beam 2150.

In another embodiment of the invention, the quadrupole magnets 2170 result in an oblong cross-sectional shape of the electron beam 2150. A projection of the oblong cross-sectional shape of the electron beam 2150 onto the X-ray generation source 2148 results in an X-ray beam that has a small spot in cross-sectional view, which is preferably substantially circular in cross-sectional shape, that is then passed through the patient 2130. The small spot is used to yield an X-ray having enhanced resolution at the patient.

Referring now to FIG. 22, in one embodiment, an X-ray is generated close to, but not in, the proton beam path. A proton beam therapy system and an X-ray system combination 2200 is illustrated in FIG. 22. The proton beam therapy system has a proton beam 268 in a transport system after the Lamberson extraction magnet 292 of the synchrotron 130. The proton beam is directed by the scanning/targeting/delivery system 140 to a tumor 1420 of a patient 1430. The X-ray system 2205 includes an electron beam source 2105 generating an electron beam 2150. The electron beam is directed to an X-ray generation source 2148, such as a piece of tungsten. Preferably, the tungsten X-ray source is located about 1, 2, 3, 5, 10, 15, 20, or 40 millimeters from the proton beam path 268. When the electron beam 2150 hits the tungsten, X-rays are generated in all directions. X-rays are blocked with a port 2262 and are selected for an X-ray beam path 2270. The X-ray beam path 2270 and proton beam path 268 run substantially in parallel as they progress to the tumor 1420. The distance between the X-ray beam path 2270 and proton beam path 269 preferably diminishes to near zero and/or the X-ray beam path 2270 and proton beam path 269 overlap by the time they reach the tumor 1420. Simple geometry shows this to be the case given the long distance, of at least a meter, between the tungsten and the tumor 1420. The distance is illustrated as a gap 2280 in FIG. 22. The X-rays are detected at an X-ray detector 2290, which is used to form an image of the tumor 1420 and/or position of the patient 1430.

As a whole, the system generates an X-ray beam that lies in substantially the same path as the proton therapy beam. The X-ray beam is generated by striking a tungsten or equivalent material with an electron beam. The X-ray generation source is located proximate to the proton beam path. Geometry of the incident electrons, geometry of the X-ray generation material, and geometry of the X-ray beam blocker 262 yield an X-ray beam that runs either in substantially in parallel with the proton beam or results in an X-ray beam path that starts proximate the proton beam path an expands to cover and transmit through a tumor cross-sectional area to strike an X-ray detector array or film allowing imaging of the tumor from a direction and alignment of the proton therapy beam. The X-ray image is then used to control the charged particle beam path to accurately and precisely target the tumor, and/or is used in system verification and validation.

Having an X-ray generation source 2148 that is proximate the proton beam path 268 allows for an X-ray of the patient 1430 to be collected close in time to use of the proton beam for tumor 1420 therapy as the X-ray generation source 2148 need not be mechanically moved prior to proton therapy. For instance, proton irradiation of the tumor 1420 occurs within about 1, 5, 10, 20, 30, or 60 seconds of when the X-ray is collected.

Referring now to FIG. 23, additional geometry of the electron beam path 2150 and X-ray beam path 2270 is illustrated. Particularly, the electron beam 350 is shown as an expanded electron beam path 2152, 2154. Also, the X-ray beam path 2270 is shown as an expanded X-ray beam path 2272, 2274.

Referring now to FIG. 24, a 3-dimensional (3-D) X-ray tomography system 2400 is presented. In a typical X-ray tomography system, the X-ray source and detector rotationally translate about a stationary subject. In the X-ray tomography system described herein, the X-ray source and detector are stationary and the patient 1430 rotates. The stationary X-ray source allows a system where the X-ray source 2148 is proximate the proton therapy beam path 268, as described supra. In addition, the rotation of the patient 1430 allows the proton dosage and/or X-ray to be distributed around the body, rather than being concentrated on one static entrance side of the body. Further, the 3-D X-ray tomography system allows for simultaneous updates of the tumor position relative to body constituents in real-time during proton therapy treatment of the tumor 1420 in the patient 1430. The X-ray tomography system is further described, infra.

In a first step of the X-ray tomography system 2400, the patient 1430 is positioned relative to the X-ray beam path 2270 and proton beam path 268 using a patient semi-immobilization/placement system, described infra. After patient 1430 positioning, a series of reference 2-D X-ray images are collected, on a detector array 2290 or film, of the patient 1430 and tumor 1420 as the subject is rotated about a y-axis 1417. For example, a series of about 50, 100, 200, or 400 X-ray images of the patient are collected as the patient is rotated. In a second example, an X-ray image is collected with each n degrees of rotation of the patient 1430, where n is about ½, 1, 2, 3, or 5 degrees of rotation. Preferably, about 200 images are collected during one full rotation of the patient through 360 degrees. Subsequently, using the reference 2-D X-ray images, an algorithm produces a reference 3-D picture of the tumor 1420 relative to the patient's constituent body parts. A tumor 1420 irradiation plan is made using the 3-D picture of the tumor 1420 and the patient's constituent body parts. Creation of the proton irradiation plan is optionally performed after the patient has moved from the X-ray imaging area.

In a second step, the patient 1430 is repositioned relative to the X-ray beam path 2270 and proton beam path 268 using the patient semi-immobilization/placement system. Just prior to implementation of the proton irradiation plan, a few comparative X-ray images of the patient 1430 and tumor 1420 are collected at a limited number of positions using the X-ray tomography system 2400 setup. For example, a single X-ray image is collected with the patient positioned straight on, at angles of plus/minus forty-five degrees, and/or at angles of plus/minus ninety degrees relative to the proton beam path 268. The actual orientation of the patient 1430 relative to the proton beam path 268 is optionally any orientation. The actual number of comparative X-ray images is also optionally any number of images, though the preferable number of comparative X-ray images is about 2 to 5 comparative images. The comparative X-ray images are compared to the reference X-ray images and differences are detected. A medical expert or an algorithm determines if the difference between the reference images and the comparative images is significant. Based upon the differences, the medical expert or algorithm determines if: proton treatment should commence, be halted, or adapted in real-time. For example, if significant differences in the X-ray images are observed, then the treatment is preferably halted and the process of collecting a reference 3-D picture of the patient's tumor is reinitiated. In a second example, if the differences in the X-ray images are observed to be small, then the proton irradiation plan commences. In a third example, the algorithm or medical expert can adapt the proton irradiation plan in real-time to adjust for differences in tumor location resulting from changes in position of the tumor 1420 in the patient 1430 or from differences in the patient 1430 placement. In the third example, the adaptive proton therapy increases patient throughput and enhances precision and accuracy of proton irradiation of the tumor 1420 relative to the healthy tissue of the patient 1430.

Patient Immobilization

Accurate and precise delivery of a proton beam to a tumor of a patient requires: (1) positioning control of the proton beam and (2) positioning control of the patient. As described, supra, the proton beam is controlled using algorithms and magnetic fields to a diameter of about 0.5, 1, or 2 millimeters. This section addresses partial immobilization, restraint, and/or alignment of the patient to insure the tightly controlled proton beam efficiently hits a target tumor and not surrounding healthy tissue as a result of patient movement.

In this section an x-, y-, and z-axes coordinate system and rotation axis is used to describe the orientation of the patient relative to the proton beam. The z-axis represent travel of the proton beam, such as the depth of the proton beam into the patient. When looking at the patient down the z-axis of travel of the proton beam, the x-axis refers to moving left or right across the patient and the y-axis refers to movement up or down the patient. A first rotation axis is rotation of the patient about the y-axis and is referred to herein as a rotation axis, bottom unit 1412 rotation axis, or y-axis of rotation. In addition, tilt is rotation about the x-axis, yaw is rotation about the y-axis, and roll is rotation about the z-axis. In this coordinate system, the proton beam path 269 optionally runs in any direction. As an illustrative matter, the proton beam path running through a treatment room is described as running horizontally through the treatment room.

In this section, a semi-vertical partial immobilization system 2500 is described, which is also illustrative of a sitting partial immobilization system or a laying positioning system.

Vertical Patient Positioning/Immobilization

Referring now to FIG. 25, the semi-vertical patient positioning system 2500 is preferably used in conjunction with proton therapy of tumors in the torso. The patient positioning and/or immobilization system controls and/or restricts movement of the patient during proton beam therapy. In a first partial immobilization embodiment, the patient is positioned in a semi-vertical position in a proton beam therapy system. As illustrated, the patient is reclining at an angle alpha, a, about 45 degrees off of the y-axis as defined by an axis running from head to foot of the patient. More generally, the patient is optionally completely standing in a vertical position of zero degrees off the of y-axis or is in a semi-vertical position alpha that is reclined about 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, or 65 degrees off of the y-axis toward the z-axis.

Patient positioning constraints 2515 are used to maintain the patient in a treatment position, including one or more of: a seat support 2520, a back support 2530, a head support 2540, an arm support 2550, a knee support 2560, and a foot support 2570. The constraints are optionally and independently rigid or semi-rigid. Examples of a semi-rigid material include a high or low density foam or a visco-elastic foam. For example the foot support is preferably rigid and the back support is preferably semi-rigid, such as a high density foam material. One or more of the positioning constraints 2515 are movable and/or under computer control for rapid positioning and/or immobilization of the patient. For example, the seat support 2520 is adjustable along a seat adjustment axis 2522, which is preferably the y-axis; the back support 2530 is adjustable along a back support axis 2532, which is preferably dominated by z-axis movement with a y-axis element; the head support 2540 is adjustable along a head support axis 2542, which is preferably dominated by z-axis movement with a y-axis element; the arm support 2550 is adjustable along an arm support axis 2552, which is preferably dominated by z-axis movement with a y-axis element; the knee support 2560 is adjustable along a knee support axis 2562, which is preferably dominated by y-axis movement with a z-axis element; and the foot support 2570 is adjustable along a foot support axis 2572, which is preferably dominated by y-axis movement with a z-axis element.

If the patient is not facing the incoming proton beam, then the description of movements of support elements along the axes change, but the immobilization elements are the same.

An optional camera 2580 is used with the patient immobilization system. The camera views the patient/subject creating an video image. The image is provided to one or more operators of the charged particle beam system and allows the operators a safety mechanism for determining if the subject has moved or desires to terminate the proton therapy treatment procedure. Based on the video image, the operators may suspend or terminate the proton therapy procedure. For example, if the operator observes via the video image that the subject is moving, then the operator has the option to terminate or suspend the proton therapy procedure.

An optional video display 2590 is provided to the patient. The video display optionally presents to the patient any of: operator instructions, system instructions, status of treatment, or entertainment.

Motors for positioning the constraints 2515, the camera 2580, and video display 2590 are preferably mounted above or below the proton path.

Respiration control is optionally performed by using the video display. As the patient breathes, internal and external structures of the body move in both absolute terms and in relative terms. For example, the outside of the chest cavity and internal organs both have absolute moves with a breath. In addition, the relative position of an internal organ relative to another body component, such as an outer region of the body, a bone, support structure, or another organ, moves with each breath. Hence, for more accurate and precise tumor targeting, the proton beam is preferably delivered at point a in time where the position of the internal structure or tumor is well defined, such as at the bottom of each breath. The video display is used to help coordinate the proton beam delivery with the patient's breathing cycle. For example, the video display optionally displays to the patient a command, such as a hold breath statement, a breath statement, a countdown indicating when a breadth will next need to be held, or a countdown until breathing may resume.

The semi-vertical patient positioning system 2500 and sitting patient positioning system are preferentially used to treatment of tumors in the head or torso due to efficiency. The semi-vertical patient positioning system 2500, sitting patient positioning system, and laying patient positioning system are all usable for treatment of tumors in the patient's limbs.

Support System Elements

Positioning constraints 2515 include all elements used to position the patient, such as those described in the semi-vertical positioning system 2500, sitting positioning system, and laying positioning system. Preferably, positioning constraints or support system elements are aligned in positions that do not impede or overlap the proton beam path 269. However, in some instances the positioning constraints are in the proton beam path 269 during at least part of the time of treatment of the patient. For instance, a positioning constraint element may reside in the proton beam path 269 during part of a time period where the patient is rotated about the y-axis during treatment. In cases or time periods that the positioning constraints or support system elements are in the proton beam path, then an upward adjustment of proton beam energy is preferably applied that increases the proton beam energy to offset the positioning constraint element impedance of the proton beam. In one case, the proton beam energy is increased by a separate measure of the positioning constraint element impedance determined during a reference scan of the positioning constraint system element or set of reference scans of the positioning constraint element as a function of rotation about the y-axis.

For clarity, the positioning constraints 2515 or support system elements are herein described relative to the semi-vertical positioning system 2500; however, the positioning elements and descriptive x-, y-, and z-axes are adjustable to fit any coordinate system, to the sitting positioning system, or the laying positioning system.

An example of a head support system is described to support, align, and/or restrict movement of a human head. The head support system preferably has several head support elements including any of: a back of head support, a right of head alignment element, and a left of head alignment element. The back of head support element is preferably curved to fit the head and is optionally adjustable along a head support axis, such as along the z-axis. Further, the head supports, like the other patient positioning constraints, is preferably made of a semi-rigid material, such as a low or high density foam, and has an optional covering, such as a plastic or leather. The right of head alignment element and left of head alignment elements or head alignment elements, are primarily used to semi-constrain movement of the head. The head alignment elements are preferably padded and flat, but optionally have a radius of curvature to fit the side of the head. The right and left head alignment elements are preferably respectively movable along translation axes to make contact with the sides of the head. Restricted movement of the head during proton therapy is important when targeting and treating tumors in the head or neck. The head alignment elements and the back of head support element combine to restrict tilt, rotation or yaw, roll and/or position of the head in the x-, y-, z-axes coordinate system.

Positioning System Computer Control

One or more of the patient positioning unit components and/or one of more of the patient positioning constraints are preferably under computer control, where the computer control positioning devices, such as via a series of motors and drives, to reproducibly position the patient. For example, the patient is initially positioned and constrained by the patient positioning constraints. The position of each of the patient positioning constraints is recorded and saved by the main controller 110, by a sub-controller or the main controller 110, or by a separate computer controller. Then, medical devices are used to locate the tumor 1420 in the patient 1430 while the patient is in the orientation of final treatment. The imaging system 170 includes one or more of: MRI's, X-rays, CT's, proton beam tomography, and the like. Time optionally passes at this point where images from the imaging system 170 are analyzed and a proton therapy treatment plan is devised. The patient may exit the constraint system during this time period, which may be minutes, hours, or days. Upon return of the patient to the patient positioning unit, the computer can return the patient positioning constraints to the recorded positions. This system allows for rapid repositioning of the patient to the position used during imaging and development of the treatment plan, which minimizes setup time of patient positioning and maximizes time that the charged particle beam system 100 is used for cancer treatment.

Patient Placement

Preferably, the patient 1430 is aligned in the proton beam path 269 in a precise and accurate manner. Several placement systems are described. The patient placement systems are described using the laying positioning system, but are equally applicable to the semi-vertical and sitting positioning systems.

In a first placement system, the patient is positioned in a known location relative to the platform. For example, one or more of the positioning constraints position the patient in a precise and/or accurate location on the platform. Optionally, a placement constraint element connected or replaceably connected to the platform is used to position the patient on the platform. The placement constraint element(s) is used to position any position of the patient, such as a hand, limb, head, or torso element.

In a second placement system, one or more positioning constraints or support element, such as the platform, is aligned versus an element in the patient treatment room. Essentially a lock and key system is optionally used, where a lock fits a key. The lock and key elements combine to locate the patient relative to the proton beam path 269 in terms of any of the x-, y-, and z-position, tilt, yaw, and roll. Essentially the lock is a first registration element and the key is a second registration element fitting into, adjacent to, or with the first registration element to fix the patient location and/or a support element location relative to the proton beam path 269. Examples of a registration element include any of a mechanical element, such as a mechanical stop, and an electrical connection indicating relative position or contact.

In a third placement system, the imaging system, described supra, is used to determine where the patient is relative to the proton beam path 269 or relative to an imaging marker placed in an support element or structure holding the patient, such as in the platform. When using the imaging system, such as an X-ray imaging system, then the first placement system or positioning constraints minimize patient movement once the imaging system determines location of the subject. Similarly, when using the imaging system, such as an X-ray imaging system, then the first placement system and/or second positioning system provide a crude position of the patient relative to the proton beam path 269 and the imaging system subsequently determines a fine position of the patient relative to the proton beam path 269.

X-Ray Synchronization with Patient Respiration

In one embodiment, X-ray images are collected in synchronization with patient respiration or breathing. The synchronization enhances X-ray image clarity by removing position ambiguity due to the relative movement of body constituents during a patient breathing cycle.

In a second embodiment, an X-ray system is orientated to provide X-ray images of a patient in the same orientation as viewed by a proton therapy beam, is synchronized with patient breathing, is operable on a patient positioned for proton therapy, and does not interfere with a proton beam treatment path. Preferably, the synchronized system is used in conjunction with a negative ion beam source, synchrotron, and/or targeting method apparatus to provide an X-ray timed with patient breathing and performed immediately prior to and/or concurrently with particle beam therapy irradiation to ensure targeted and controlled delivery of energy relative to a patient position resulting in efficient, precise, and/or accurate noninvasive, in-vivo treatment of a solid cancerous tumor with minimization of damage to surrounding healthy tissue in a patient using the proton beam position verification system.

An X-ray delivery control algorithm is used to synchronize delivery of the X-rays to the patient 1430 within a given period of each breath, such as at the top or bottom of a breath when the subject is holding their breath. For clarity of combined X-ray images, the patient is preferably both accurately positioned and precisely aligned relative to the X-ray beam path 2270. The X-ray delivery control algorithm is preferably integrated with the breathing control module. Thus, the X-ray delivery control algorithm knows when the subject is breathing, where in the breath cycle the subject is, and/or when the subject is holding their breath. In this manner, the X-ray delivery control algorithm delivers X-rays at a selected period of the breathing cycle. Accuracy and precision of patient alignment allow for (1) more accurate and precise location of the tumor 1420 relative to other body constituents and (2) more accurate and precise combination of X-rays in generation of a 3-dimensional X-ray image of the patient 1430 and tumor 1420.

Referring now to FIG. 26, an example of generating an X-ray image 2600 of the patient 1430 and tumor 1420 using the X-ray generation device 2100 or 3-dimensional X-ray generation device 2100 as a known function of time of the patient's breathing cycle is provided. In one embodiment, as a first step the main controller 110 instructs, monitors, and/or is informed of patient positioning 2610. In a first example of patient positioning 2610, an automated patient positioning system, under main controller 110 control, is used to align the patient 1430 relative to the X-ray beam path 2270. In a second example of patient positioning, the main controller 110 is told via sensors or human input that the patient 1430 is aligned. In a second step, patient breathing is then monitored 2620, as described infra. As a first example of respiration monitoring, an X-ray is collected 2640 at a known point in the patient respiration cycle. In a second example of respiration monitoring, the patient's respiration cycle is first controlled in a third step of controlling patient breathing 2630 and then as a fourth step an X-ray is collected 2640 at a controlled point in the patient breathing cycle. Preferably, the cycle of patient positioning 2610, patient breath monitoring 2620, patient breath control 2630, and collecting an X-ray 2640 is repeated with different patient positions. For example, the patient 1430 is rotated about an axis 1417 and X-rays are collected as a function of the rotation. In a fifth step, a 3-dimensional X-ray image 2650 is generated of the patient 1430, tumor 1420, and body constituents about the tumor using the collected X-ray images, such as with the 3-dimensional X-ray generation device 2100, described supra. The patient breath monitoring and control steps are further described, infra.

Patient Breathing Monitoring

Preferably, the patient's breathing pattern is monitored 2620. When a subject or patient 1430 is breathing many portions of the body move with each breath. For example, when a subject breathes the lungs move as do relative positions of organs within the body, such as the stomach, kidneys, liver, chest muscles, skin, heart, and lungs. Generally, most or all parts of the torso move with each breath. Indeed, the inventors have recognized that in addition to motion of the torso with each breath, various motion also exists in the head and limbs with each breath. Motion is to be considered in delivery of a proton dose to the body as the protons are preferentially delivered to the tumor and not to surrounding tissue. Motion thus results in an ambiguity in where the tumor resides relative to the beam path. To partially overcome this concern, protons are preferentially delivered at the same point in each of a series of breathing cycles.

Initially a rhythmic pattern of breathing of a subject is determined 2620. The cycle is observed or measured. For example, an X-ray beam operator or proton beam operator can observe when a subject is breathing or is between breaths and can time the delivery of the protons to a given period of each breath. Alternatively, the subject is told to inhale, exhale, and/or hold their breath and the protons are delivered during the commanded time period.

Preferably, one or more sensors are used to determine the breathing cycle of the individual. Two examples of a breath monitoring system are provided: (1) a thermal monitoring system and (2) a force monitoring system.

A first example of the thermal breath monitoring system is provided. In the thermal breath monitoring system, a sensor is placed by the nose and/or mouth of the patient. As the jaw of the patient is optionally constrained, as described supra, the thermal breath monitoring system is preferably placed by the patient's nose exhalation path. To avoid steric interference of the thermal sensor system components with proton therapy, the thermal breath monitoring system is preferably used when treating a tumor not located in the head or neck, such as a when treating a tumor in the torso or limbs. In the thermal monitoring system, a first thermal resistor 2595 is used to monitor the patient's breathing cycle and/or location in the patient's breathing cycle. Preferably, the first thermal resistor 2595 is placed by the patient's nose, such that the patient exhaling through their nose onto the first thermal resistor 2595 warms the first thermal resistor 2595 indicating an exhale. Preferably, a second thermal resistor operates as an environmental temperature sensor. The second thermal resistor is preferably placed out of the exhalation path of the patient but in the same local room environment as the first thermal resistor 2595. Generated signal, such as current from the thermal resistors 2595, is preferably converted to voltage and communicated with the main controller 110 or a sub-controller of the main controller. Preferably, the second thermal resistor is used to adjust for the environmental temperature fluctuation that is part of a signal of the first thermal resistor 2595, such as by calculating a difference between values of the thermal resistors 2595 to yield a more accurate reading of the patient's breathing cycle.

A second example of the force/pressure breath monitoring system is provided. In the force breath monitoring system, a sensor is placed by the torso. To avoid steric interference of the force sensor system components with proton therapy, the force breath monitoring system is preferably used when treating a tumor located in the head, neck, or limbs. In the force monitoring system, a belt or strap 2555 is placed around an area of the patient's torso that expands and contracts with each breath cycle of the patient. The belt 2555 is preferably tight about the patient's chest and is flexible. A force meter 2557 is attached to the belt and senses the patients breathing pattern. The forces applied to the force meter 2557 correlate with periods of the breathing cycle. The signals from the force meter 2557 are preferably communicated with the main controller 110 or a sub-controller of the main controller.

Respiration Control

Referring now to FIG. 26, once the rhythmic pattern of the subject's respiration or breathing is determined, a signal is optionally delivered to the subject to more precisely control the breathing frequency 2630. For example, a display screen 2590 is placed in front of the subject directing the subject when to hold their breath and when to breath. Typically, a respiration control module uses input from one or more of the breathing sensors. For example, the input is used to determine when the next breath exhale is to complete. At the bottom of the breath, the control module displays a hold breath signal to the subject, such as on a monitor, via an oral signal, digitized and automatically generated voice command, or via a visual control signal. Preferably, a display monitor 2590 is positioned in front of the subject and the display monitor displays breathing commands to the subject. Typically, the subject is directed to hold their breath for a short period of time, such as about ½, 1, 2, 3, 5, or 10 seconds. The period of time the breath is held is preferably synchronized to the delivery time of the proton beam to the tumor, which is about ½, 1, 2, or 3 seconds. While delivery of the protons at the bottom of the breath is preferred, protons are optionally delivered at any point in the breathing cycle, such as upon full inhalation. Delivery at the top of the breath or when the patient is directed to inhale deeply and hold their breath by the respiration control module is optionally performed as at the top of the breath the chest cavity is largest and for some tumors the distance between the tumor and surrounding tissue is maximized or the surrounding tissue is rarefied as a result of the increased volume. Hence, protons hitting surrounding tissue is minimized. Optionally, the display screen tells the subject when they are about to be asked to hold their breath, such as with a 3, 2, 1, second countdown so that the subject is aware of the task they are about to be asked to perform.

Proton Beam Therapy Synchronization with Respiration

A proton delivery control algorithm is used to synchronize delivery of the protons to the tumor within a given period of each breath, such as at the top or bottom of a breath when the subject is holding their breath. The proton delivery control algorithm is preferably integrated with the respiration control module. Thus, the proton delivery control algorithm knows when the subject is breathing, where in the breath cycle the subject is, and/or when the subject is holding their breath. The proton delivery control algorithm controls when protons are injected and/or inflected into the synchrotron, when an RF signal is applied to induce an oscillation, as described supra, and when a DC voltage is applied to extract protons from the synchrotron, as described supra. Typically, the proton delivery control algorithm initiates proton inflection and subsequent RF induced oscillation before the subject is directed to hold their breath or before the identified period of the breathing cycle selected for a proton delivery time. In this manner, the proton delivery control algorithm can deliver protons at a selected period of the breathing cycle by simultaneously or nearly simultaneously delivering the high DC voltage to the second pair of plates, described supra, which results in extraction of the protons from the synchrotron and subsequent delivery to the subject at the selected time point. Since the period of acceleration of protons in the synchrotron is constant or known for a desired energy level of the proton beam, the proton delivery control algorithm is used to set an AC RF signal that matches the breathing cycle or directed breathing cycle of the subject.

Although the invention has been described herein with reference to certain preferred embodiments, one skilled in the art will readily appreciate that other applications may be substituted for those set forth herein without departing from the spirit and scope of the present invention. Accordingly, the invention should only be limited by the Claims included below. 

1. An apparatus for radiation therapy of a tumor of a patient with charged particles from a charged particle cancer therapy system, comprising: a charged particle beam path, said charged particle beam path sequentially traversing: an injector, a synchrotron; and a beam transport system, wherein said synchrotron comprises an extraction foil.
 2. The apparatus of claim 1, wherein the charged particles run through said charged particle beam path during operation of said charged particle cancer therapy system.
 3. The apparatus of claim 1, said injector further comprising: an ion beam generation source; and a magnetic material centrally positioned within said ion beam generation source, said magnetic material creating a magnetic field barrier between a high temperature plasma zone within said ion beam generation source and a low temperature plasma region, wherein a portion of said charged particle beam path circumferentially surrounds (1) negative ions formed in said low temperature plasma region and (2) a negative ion beam resulting from extraction of the negative ions from the low temperature plasma region.
 4. The apparatus of claim 1, wherein said synchrotron further comprises: a center; a pair of oscillation inducing blades spanning said charged particle beam path, said pair of oscillation blades comprising a first distance from said center of said synchrotron; a pair of extraction blades spanning said charged particle beam path, said pair of extraction blades comprising a second distance from said center of said synchrotron, said first distance greater than said second distance; and a deflector about said charged particle beam path.
 5. The apparatus of claim 1, further comprising: a statically positioned X-ray generation source, said X-ray generation source located within about forty millimeters of said charged particle beam path.
 6. The apparatus of claim 1, wherein said synchrotron further comprises: exactly four turning sections, wherein each of said turning sections bends said charged particle beam path about ninety degrees.
 7. The apparatus of claim 1, wherein said synchrotron further comprises: four turning sections; and bending magnets, wherein each of said four turning sections comprises at least four of said bending magnets, wherein said charged particle beam path runs through each of said four turning sections.
 8. The apparatus of claim 1, wherein said synchrotron comprises an equal number of turning sections and straight sections.
 9. The apparatus of claim 1, wherein said charged particle beam path connects to: a carbon input foil in said injector; an aluminum output foil positioned (1) after said synchrotron and (2) across said charged particle beam, wherein said output foil has a first side; and a beam position verification layer substantially in contact with said first side of said output foil, wherein said verification layer comprises photon emitting centers.
 10. The apparatus of claim 1, further comprising: a first foil; a second foil; and a third foil, wherein each of said first foil, said second foil, and said third foil axially crosses said charged particle beam path.
 11. A method for radiation therapy of a tumor of a patient with treatment particles from a charged particle cancer therapy system, comprising sequential steps of: accelerating circulating charged particles in a synchrotron yielding accelerated charged particles; inducing oscillation of the accelerated charged particles yielding oscillating charged particles; extracting the oscillating charged particles from said synchrotron using an extraction foil yielding reduced energy charged particles; and transporting the reduced energy charged particles to the tumor, wherein a charged particle beam path initiates in an injector, wherein said charged particle beam path circumferentially surrounds the charged particles in said synchrotron, wherein at least a portion of said charged particle beam path circumferentially surrounds at least a portion of all of: (1) the charged particles; (2) the accelerated charged particles; (3) the oscillating charged particles; and (4) the reduced energy charged particles.
 12. The method of claim 11, further comprising the step of: generating the treatment particles in an injector; passing the treatment particles through an input foil in said injector; maintaining a first vacuum in said charged particle beam path on a first side of said input foil; maintaining a second vacuum within said charged particle beam path on a second side of said input foil, wherein a first pressure of said first vacuum does not equal a second pressure of said second vacuum; and injecting the treatment particles into said synchrotron, wherein circulation of the treatment particles in said synchrotron yields the circulating charged particles.
 13. The method of claim 11, further comprising the steps of: generating X-rays with an X-ray generation source located within about forty millimeters of said charged particle beam path, wherein said X-ray source maintains a single static position: (1) during use of said X-ray source and (2) during tumor treatment with the charged particle beam, wherein, for a distance, the X-rays emitted from said X-ray source run substantially in parallel with the charged particles.
 14. The method of claim 11, further comprising the steps of: extracting the reduced energy charged particles from said synchrotron; and controlling an intensity of the reduced energy charged particles, wherein said step of controlling said intensity occurs prior to the charged particles passing through a Lamberson extraction magnet in said synchrotron.
 15. The method of claim 11, further comprising the steps of: rotating a rotatable platform to at least five irradiation positions covering at least ninety degrees of rotation; and irradiating the tumor with the reduced energy charged particles during each of said at least five irradiation positions, said rotatable platform configured to rotate the tumor.
 16. The method of claim 11, further comprising the steps of: generating an ion beam in an ion beam generation source of said injector; creating a magnetic field barrier between a high temperature plasma zone within said ion beam generation source and a low temperature plasma region using a magnetic material centrally positioned within said ion beam generation source, wherein said charged particle beam path initiates with negative ions formed in said low temperature plasma region; and extracting the negative ions from said low temperature plasma region forming a negative ion beam, wherein a length of said charged particle beam path circumferentially surrounds said negative ion beam.
 17. The method of claim 11, further comprising the step of: forming a vacuum barrier with an output foil between atmosphere and a first portion of said charged particle beam path within said synchrotron, wherein said output foil comprises a first surface, wherein a coating substantially covers at least a portion of said first surface of said output foil, said coating configured to emit photons when struck by the reduced energy charged particles, and wherein said extraction foil comprises a thickness of less than about one hundred micrometers.
 18. The method of claim 11, wherein said extraction foil consists essentially of atoms having six or fewer protons per atom.
 19. The method of claim 11, further comprising the step of: generating X-rays with a statically positioned X-ray generation source, said X-ray generation source located within about forty millimeters of said charged particle beam path.
 20. The method of claim 11, further comprising the step of: rotating a rotatable platform under a distal end of said charged particle beam path, wherein said rotatable platform rotates around an axis aligned with gravity during use; and controlling the treatment particles exiting said synchrotron in terms of all of: timing, extraction energy, and extraction intensity. 